Drug delivery implant and a method using the same

ABSTRACT

A drug delivery implant and a method of using the same are disclosed herein. In one or more embodiments, the method includes forming a pocket in the cornea of the eye to gain access to tissue surrounding the pocket; applying a photosensitizer inside the pocket so the photosensitizer permeates at least a portion of the tissue surrounding the pocket and facilitates cross-linking of the tissue surrounding the pocket; irradiating the cornea to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket; and before or after the portion of the tissue surrounding the pocket has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, inserting a corneal drug delivery implant into the pocket configured to release one or more medications into the eye.

CROSS-REFERENCE TO RELATED APPLICATIONS

This patent application claims priority to U.S. Provisional Patent Application No. 62/423,734, entitled “Drug Delivery Implant And A Method Using The Same”, filed on Nov. 17, 2016, and is a continuation-in-part of application Ser. No. 15/653,053, entitled “Corneal Intraocular Pressure Sensor And A Surgical Method Using The Same”, filed Jul. 18, 2017, now U.S. Pat. No. 10,206,569, which claims priority to U.S. Provisional Patent Application No. 62/363,382, entitled “Corneal Intraocular Pressure Sensor And A Surgical Method Using The Same”, filed on Jul. 18, 2016, and Ser. No. 15/653,053 is a continuation-in-part of application Ser. No. 15/631,219, entitled “Method of Prevention of Capsular Opacification and Fibrosis After Cataract Extraction and/or Prevention of Fibrosis Around a Shunt or Stent After Glaucoma Surgery”, filed Jun. 23, 2017, now U.S. Pat. No. 10,195,081, which claims priority to U.S. Provisional Patent Application No. 62/353,632, entitled “Method of Prevention of Capsular Opacification and Fibrosis After Cataract Extraction and/or Prevention of Fibrosis Around a Shunt or Stent After Glaucoma Surgery”, filed on Jun. 23, 2016, and Ser. No. 15/631,219 is a continuation-in-part of application Ser. No. 15/285,375, entitled “Method of Preventing Capsular Opacification and Fibrosis Utilizing an Accommodative Intraocular Lens Implant”, filed Oct. 4, 2016, now U.S. Pat. No. 9,744,029, which claims priority to U.S. Provisional Patent Application No. 62/360,439, entitled “Method of Preventing Capsular Opacification and Fibrosis with the Creation of an Accommodative Intraocular Lens”, filed on Jul. 10, 2016, and Ser. No. 15/285,375 is a continuation-in-part of application Ser. No. 15/230,445, entitled “Corneal Lenslet Implantation With A Cross-Linked Cornea”, filed Aug. 7, 2016, now U.S. Pat. No. 9,937,033, which claims priority to U.S. Provisional Patent Application No. 62/360,281, entitled “Method of Altering the Refractive Properties of an Eye”, filed on Jul. 8, 2016, and Ser. No. 15/230,445 is a continuation-in-part of application Ser. No. 14/709,801, entitled “Corneal Transplantation With A Cross-Linked Cornea”, filed May 12, 2015, now U.S. Pat. No. 9,427,355, which claims priority to U.S. Provisional Patent Application No. 61/991,785, entitled “Corneal Transplantation With A Cross-Linked Cornea”, filed on May 12, 2014, and to U.S. Provisional Patent Application No. 62/065,714, entitled “Corneal Transplantation With A Cross-Linked Cornea”, filed on Oct. 19, 2014, the disclosure of each of which is hereby incorporated by reference as if set forth in their entirety herein.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

Not Applicable.

NAMES OF THE PARTIES TO A JOINT RESEARCH AGREEMENT

Not Applicable.

INCORPORATION BY REFERENCE OF MATERIAL SUBMITTED ON A COMPACT DISK

Not Applicable.

BACKGROUND OF THE INVENTION 1. Field of the Invention

The invention generally relates to a drug delivery implant and a method using the same. More particularly, the invention relates to a drug delivery implant that may be inserted into a cross-linked pocket formed in the cornea of the eye. The drug delivery implant described herein also may be used for parts of the body other than the eye.

2. Background

Corneal scarring is a major cause of blindness, especially in developing countries. There are various causes for corneal scarring, which include: bacterial infections, viral infections, fungal infections, parasitic infections, genetic corneal problems, Fuch's dystrophy, and other corneal dystrophies. A corneal transplant is often required if the corneal scarring is extensive, and cannot be corrected by other means. However, there can be major complications associated with a corneal transplant, such as corneal graft rejection wherein the transplanted cornea is rejected by the patient's immune system.

A normal emmetropic eye includes a cornea, a lens and a retina. The cornea and lens of a normal eye cooperatively focus light entering the eye from a far point, i.e., infinity, onto the retina. However, an eye can have a disorder known as ametropia, which is the inability of the lens and cornea to focus the far point correctly on the retina. Typical types of ametropia are myopia, hypermetropia or hyperopia, and astigmatism.

A myopic eye has either an axial length that is longer than that of a normal emmetropic eye, or a cornea or lens having a refractive power stronger than that of the cornea and lens of an emmetropic eye. This stronger refractive power causes the far point to be projected in front of the retina.

Conversely, a hypermetropic or hyperopic eye has an axial length shorter than that of a normal emmetropic eye, or a lens or cornea having a refractive power less than that of a lens and cornea of an emmetropic eye. This lesser refractive power causes the far point to be focused behind the retina.

An eye suffering from astigmatism has a defect in the lens or shape of the cornea converting an image of the point of light to a line. Therefore, an astigmatic eye is incapable of sharply focusing images on the retina.

While laser surgical techniques, such as laser-assisted in situ keratomileusis (LASIK) and photorefractive keratectomy (PRK) are known for correcting refractive errors of the eye, these laser surgical techniques have complications, such as post-operative pain and dry eye. Also, these laser surgical techniques cannot be safely used on patients with corneas having certain biomechanical properties. For example, corneal ectasia may occur if these laser surgical techniques are applied to patients having thin corneas (e.g., corneas with thicknesses that are less than 500 microns).

Therefore, what is needed is a method for corneal transplantation that reduces the likelihood that the implanted cornea will be rejected by the patient. Moreover, a method is needed for corneal transplantation that is capable of preserving the clarity of the transplanted cornea. Furthermore, there is a need for a method of corneal transplantation that reduces the likelihood that the transplanted cornea will be invaded by migrating cells. Also, what is needed is a method for corneal lenslet implantation for modifying the cornea to better correct ametropic conditions. In addition, a method is needed for corneal lenslet implantation that prevents a lens implant from moving around inside the cornea once implanted so that the lens implant remains centered about the visual axis of the eye.

Moreover, many cataract patients experience complications following their cataract surgery. For example, opacification of the lens capsule affects about 80-90% of the eyes after cataract surgery because of proliferation of the remaining cells in the lens capsule. This post-surgery opacification requires a laser disruption of the posterior capsule for the patient to see. Also, conventional monofocal intraocular lenses do not permit accommodation. As such, patients with monofocal intraocular lenses typically require reading glasses after cataract surgery.

Therefore, it is apparent that a need also exists for treatment of cell proliferation of the lens capsule after cataract extraction, and for an accommodative intraocular lens implant that enables the cataract patient to see both far and near objects without the need for supplemental lenses, such as reading glasses.

Furthermore, cataract patients who additionally have glaucoma pose difficult challenges for the treating ophthalmologist. When glaucoma is associated with a cataract in the same patient, the two surgeries must often be performed at the same time. However, unfortunately, both conditions can have their own complications. For example, as mentioned above, opacification of the lens capsule affects about 80-90% of the eyes after cataract surgery because of proliferation of the remaining cells in the lens capsule. This post-surgery opacification requires a laser disruption of the posterior capsule for the patient to see. Similarly, after glaucoma surgery, the connecting hole from the eye to the subconjunctival space may become plugged by fibrous proliferation occurring after surgery in an attempt to reject the shunt after the surgery or even a shunt in place, as a response of the surgical procedure creating a hole in the eye wall to drain the intraocular fluid.

Therefore, it is apparent that a need further exists for treatment of cell proliferation of the lens capsule after cataract extraction, and for treatment of fibrous cell proliferation after glaucoma surgery with or without a drainage tube.

Glaucoma is a disease that affects the eye and is considered one of the major causes of blindness in the world. There are many forms of glaucoma, having different pathogenesis. Among these are open angle glaucoma (OAG) where the anterior chamber located between the cornea and the iris is open, closed angle glaucoma where the anterior chamber angle is closed, and secondary glaucoma caused by different etiologies, but often an inflammatory process proceeds its occurrence. The glaucoma can be congenital or acquired, and some have genetic predisposition. Regardless of its pathogenesis, the hallmark of the disease is mostly an increased intraocular pressure (IOP), except for in the low tension glaucoma where the IOP appears to be normal, but the patient has the other symptoms of glaucoma. The other characteristic findings in glaucoma eyes are the cupping of the optic nerve head, and the loss of the nerve fiber layer of the retina and ganglion cells of the retina. These can lead to, or can also be considered a consequence of a degenerative process affecting potentially the retinal ganglion cells and an imbalance of the IOP and intracranial pressure leading to gradual loss of the visual field that can be constricted with time or completely lost resulting in blindness.

There are many treatment modalities in managing the disease processes. Since the IOP is, in most cases, elevated beyond a normal level of 10-20 mmHg, routine checking of the IOP including potentially a 24-hour or more measuring of these values during the day and night is needed to find out if there are any pressure variations during the course of the day, especially during sleep where the IOP generally is raised. These pressure variations can obviously compromise the retinal nerves and circulation, even if the pressure is within a normal range of 10-20 mmHg, such as in patients with low tension glaucoma. Thus far, the measurement of the IOP has been sporadic because it is limited by a patient's visit to the doctor's office.

The treatment for glaucoma has been mostly medicinal, that is by applying antiglaucoma medication(s) as eye drops to reduce the intraocular pressure. If the IOP cannot be controlled, either by laser surgery of the angle or ciliary body processes where the fluid is produced, then alternatively, one tries to drain the intraocular fluid to outside of the eye through a stent or shunt opening with one end in the anterior chamber and the other end located in the subconjunctival space or connecting the intraocular fluid via a shunt tube from the inside the eye to the choroidal space. In some situations, the surgeon makes a small hole in the eye wall connecting the anterior chamber fluid or aqueous directly to the subconjunctival space. There are a number of variations of this surgery having the same goal of reducing the IOP to a normal level. The glaucoma can also be associated with a cataract and not seldom requires doing the two surgeries at the same time. However, unfortunately both conditions can have their own complications (e.g., opacification of the lens capsule after cataract surgery affecting about 80-90% percent of the eyes because of proliferation of the remaining cells in the lens capsule, and requiring a laser disruption of the posterior capsule for the patient to see). Similarly, after glaucoma surgery, the connecting hole from the eye to the subconjunctival space can become plugged by fibrous proliferation occurring after surgery with or without a shunt tubing.

Recently, efforts have been made experimentally to measure the intraocular pressure via a contact lens positioned on the surface of the cornea for a duration of 24 hours with a pressure sensor and transmit the information wirelessly to a receiver mounted on an eye glass frame. The disadvantage of this contact lens system is that the system provides the measurement of the IOP indirectly from the eye cavity and depends on how the corneal curvature is deformed in response to the IOP. Also, the contact lens can be worn only for a short time because, otherwise it can interfere with the corneal oxygenation that happens mostly from the outside air and nutrition of the cornea that is, in part, supplied by the tear film that is compromised by placement of a static contact lens on the cornea. The chances of a corneal abrasion is increased by the described shortcomings, and for the patient, the placement and removal of the contact lens is particularly difficult in elderly patients.

Another recent effort has implanted such a system inside the lens capsule of the eye, by removing the natural crystalline lens, but leaving the lens capsule intact so that the device can be positioned inside the lens capsule and measure the IOP, and then transmit it outside the eye to a receiver. Because the system disposed in the lens capsule requires a battery to operate, the eventual need to replace the battery necessitates another surgical procedure to be performed later. Also, the initial surgical procedure has its own serious complications, and often is not justified when one is dealing with young patients or children. In addition, this process creates capsular opacification, it deprives the patient from the use of his or her natural lens, and can have the lifelong potential complication of inflammation that aggravates the existing glaucoma itself.

Therefore, it is apparent that a need further exists for an intraocular pressure measurement device and a method using the same that eliminates the shortcomings of the aforedescribed procedures.

Further, conventional ocular drug delivery systems include medication dissolved or suspended in a physiological solutions applied as drops to the cornea and conjunctiva bathing the superficial structure of the eye. The drops can have also particulate matter for faster tissue penetration or slow release of medication potentially lasting 1-2 days or months, etc. The medication, when applied as drops, partially penetrates the barrier of the corneal epithelium and reaches in sufficient concentration in the aqueous fluid of the anterior chamber. The aqueous is constantly produced in the eye from the ciliary body epithelium in the back or the iris in the posterior chamber and moves through the pupil in the anterior chamber, and is removed from the eye through the trabecular meshwork located in the angle of the eye between the iris and the cornea. A part of the aqueous mixes with the vitreous. In general, topically-applied medication reaches the back of the eye in lower concentrations and slower than when injected in the vitreous cavity.

The injection of medication in the eye cavity, in the form of solution or micro-particulates, can bypass the ocular barrier and effectively treat the retinal and choroidal diseases, for months. Therefore, they have to be reinjected frequently in chronic disease of the eye.

The polymeric slow release systems release the medication inside the eye and have been implanted in the vitreous cavity, over or under the retina, providing medication only to the back of the eye for a period of 3 months to a year.

In general, a drug delivery device has been implanted in most places of the eye, except in the cornea. A non-biodegradable device can be injected in the vitreous cavity if they are very small otherwise, they can move around scratching the retina or move to the anterior chamber damaging the corneal endothelial cells. However, they can be sutured in the sclera with their anchoring section, while the drug delivery section is located inside the eye, i.e., in the vitreous cavity to release the medication.

These devices, in general, initiate a foreign body response associated with fibroblast cell migration around the device, and the device becomes encapsulated, making the amount of drug release unpredictable through the thick fibrotic scar tissue.

Similarly, stem cellular drug delivery devices, such as ciliary body neurotrophic factors that produce needed factors for the retinal survival in certain degenerative diseases can be only be implanted inside the vitreous cavity where it is considered an immune-privileged space. Otherwise, it becomes encapsulated by the scar tissue and become less effective. The vitreous cavity is considered an immune privileged space meaning that blood vessels have no access to it to produce a cellular immune response that would attack and destroy the stem cells or surround a device with a fibrous membrane which would make the system useless.

To date, in general, the cornea has not been considered a suitable location to implant a slow release drug delivery device because of concern that it becomes vascularized affecting the transparency of cornea, which is vital for passing the light through it to reach the photoreceptors of the retina creating sensation of vision.

Therefore, it is apparent that a need exists for a drug delivery implant and a method using the same that is capable of effectively delivering medications to the cornea of the eye and to parts of the body other than the cornea of the eye.

BRIEF SUMMARY OF EMBODIMENTS OF THE INVENTION

Accordingly, the present invention is directed to a drug delivery implant and a method using the same that substantially obviates one or more problems resulting from the limitations and deficiencies of the related art.

In accordance with one or more embodiments of the present invention, there is provided a method of implanting a corneal drug delivery implant in an eye of a patient. The method comprising the steps of: (i) forming a pocket in the cornea of the eye so as to gain access to tissue surrounding the pocket; (ii) after the pocket in the cornea has been formed, applying a photosensitizer inside the pocket so that the photosensitizer permeates at least a portion of the tissue surrounding the pocket, the photosensitizer facilitating cross-linking of the tissue surrounding the pocket; (iii) irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket; and (iv) before or after the portion of the tissue surrounding the pocket has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, inserting a corneal drug delivery implant into the pocket, the corneal drug delivery implant configured to release one or more medications into the eye of the patient.

In a further embodiment of the present invention, the step of forming a pocket in the cornea of the eye further comprises cutting out a three-dimensional portion of stromal tissue from the cornea of the eye using a femtosecond laser; and removing the three-dimensional cut portion of the cornea using forceps so as to create a three-dimensional pocket for receiving the corneal drug delivery implant so that the corneal drug delivery implant does not exert any pressure on the stromal tissue of the cornea.

In yet a further embodiment, the method further comprises the step of: (v) prior to forming the pocket in the cornea of the eye, bleaching out any peripheral conjunctival capillaries that are present with a low dose of a vasoconstrictive medication and/or a low dose of hyaluronic acid in a fluid in order to make the corneal limbus area transparent prior to applying the femtosecond laser.

In still a further embodiment, the three-dimensional pocket is formed in a peripheral portion of the cornea between the cornea and the anterior sclera of the eye.

In yet a further embodiment, the three-dimensional pocket formed in the peripheral portion of the cornea extends between 1 degree and 360 degrees around the corneal periphery.

In still a further embodiment, the three-dimensional pocket has a width between approximately 0.05 millimeters and approximately 8 millimeters, inclusive.

In yet a further embodiment, the step of applying the photosensitizer further comprises applying the photosensitizer on the surface of the cornea to penetrate the corneal stroma followed by incising the pocket in the cornea and crosslinking the cornea.

In yet a further embodiment, the step of applying the photosensitizer inside the pocket comprises injecting the photosensitizer inside the pocket using a needle.

In still a further embodiment, the step of injecting the photosensitizer inside the pocket using the needle comprises injecting the photosensitizer such that the photosensitizer penetrates at least 20 microns beyond a wall of the pocket in the stromal tissue of the cornea.

In yet a further embodiment, the method further comprises the step of: (v) injecting 0.01 milliliters to 0.1 milliliters of a 0.02 to 2% lidocaine or bupivacaine solution alone or together with the photosensitizer so as to anesthetize the cornea for between 1 to 15 hours, thereby eliminating a pain sensation or discomfort during the surgical procedure.

In still a further embodiment, the photosensitizer comprises riboflavin.

In yet a further embodiment, the step of creating a pocket in the cornea of the eye further comprises forming a circular-shaped pocket, a semi-circular-shaped pocket, a C-shaped pocket, a doughnut-shaped pocket, or a rectangular-shaped pocket in the cornea of the eye, and with or without removing the tissue inside the circular-shaped pocket, the semi-circular-shaped pocket, the C-shaped pocket, the doughnut-shaped pocket, or the rectangular-shaped pocket.

In still a further embodiment, the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises irradiating the cornea with ultraviolet light, another wavelength of light, microwaves, or combinations thereof.

In yet a further embodiment, the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises inserting a fiber optic into the pocket and irradiating the cornea with light emitted from the fiber optic so as to activate the cross-linkers in the portion of the tissue surrounding the pocket.

In still a further embodiment, the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises irradiating the cornea from outside the eye.

In yet a further embodiment, the method further comprises the step of: (v) prior to the insertion of the corneal drug delivery implant into the pocket, injecting a predetermined amount of hyaluronic acid or a viscous biocompatible material into the pocket so as to simplify the insertion of the corneal drug delivery implant in the pocket.

In still a further embodiment, the corneal drug delivery implant is formed from a biocompatible organic material, a biocompatible non-organic material, or a combination of a biocompatible organic material and a biocompatible non-organic material. The material forming the drug delivery implant may be viscous, solid, or semisolid.

In yet a further embodiment, the corneal drug delivery implant is formed from polylactic acid, polyglycolic acid, polycaprolactone, another biodegradable polymer, silicone, acrylic, methacrylate, hydroxyethyl methacrylate (HEMA), a metallic material (e.g., gold), a non-metallic material (e.g., glass), or combinations thereof. The drug delivery implant may be solid, tubular, or porous.

In still a further embodiment, the corneal drug delivery implant is coated with a biocompatible material, the biocompatible material selected from the group consisting of collagen, elastin, polyethylene glycol, biotin, streptavidin, and combinations thereof. The corneal drug delivery implant may also be coated with various nanoparticles.

In yet a further embodiment, the method further comprises the step of: (v) replacing the corneal drug delivery implant in the pocket with a replacement corneal drug delivery implant after the corneal drug delivery implant is no longer functional or when the medication in the corneal drug delivery implant has been exhausted.

In still a further embodiment, the corneal drug delivery implant further comprises a needle configured to fluidly couple the corneal drug delivery implant with the aqueous fluid in the anterior chamber of the eye; and the method further comprises the step of: (v) penetrating the anterior chamber of the eye using the needle, an open end of the needle opening into the anterior chamber of the eye so as to allow the medication from the corneal drug delivery implant to be delivered to the anterior chamber of the eye and/or enable an aqueous biopsy to be obtained from the aqueous fluid of the eye.

In yet a further embodiment, the method further comprises, prior to inserting the corneal drug delivery implant into the pocket, the steps of: (v) coating an outer surface of the corneal drug delivery implant with an organic material configured to absorb a photosensitizer; (vi) immersing the corneal drug delivery implant in a biocompatible solution comprising the photosensitizer so that the photosensitizer is able to diffuse out of the organic material coating of the corneal drug delivery implant after the corneal drug delivery implant is inserted into the pocket; and (vii) after the corneal drug delivery implant is inserted into the pocket, irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket.

In still a further embodiment, the photosensitizer in the biocompatible solution comprises riboflavin nanoparticles; and the method further comprises the step of: (v) slowly releasing the medication of the corneal drug delivery implant into the cornea of the eye without being inhibited by vascular growth around the corneal drug delivery implant.

In yet a further embodiment, the method further comprises the step of: (v) after the implantation of the corneal drug delivery implant, applying the photosensitizer one or more additional times inside the space between the corneal drug delivery implant and the surrounding corneal tissue, and irradiating the cornea one or more additional times with ultraviolet radiation to cross-link the tissue surrounding the corneal drug delivery implant so as to prevent encapsulation of the corneal drug delivery implant and cellular migration towards the corneal drug delivery implant.

In still a further embodiment, the step of applying the photosensitizer one or more additional times inside the space between the corneal drug delivery implant and the surrounding corneal tissue further comprises injecting the photosensitizer inside the space between the corneal drug delivery implant and the surrounding corneal tissue by using a 33 gauge needle.

In yet a further embodiment, the corneal drug delivery implant comprises a tubular body portion with a circular sidewall and oppositely disposed ends, the circular sidewall of the tubular body portion being solid and one of the oppositely disposed ends being open or the circular sidewall of the tubular body portion comprising a plurality of holes therein and the oppositely disposed ends being solid.

In still a further embodiment, the method further comprises the step of: (v) prior to the implantation of the corneal drug delivery implant, constructing the corneal drug delivery implant in vitro by three-dimensionally printing the corneal drug delivery implant to a desired shape and size.

In yet a further embodiment, the method further comprising the step of: (v) prior to the implantation of the corneal drug delivery implant, forming the corneal drug delivery implant into a shape selected from the group consisting of a rod shape, a C-shape, a semi-circular shape, a doughnut shape, or a rectangular flat tube shape.

In still a further embodiment, the medication of the corneal drug delivery implant is selected from the group consisting of an anti-inflammatory, an anti-infective, an immune-suppressant, an anti-VEGF, a biologic, an anti-PDGF, an Anti IL-6, a Rho kinase inhibitor, Brimonidine, a nerve growth factor, an anti-glaucoma medication, and combinations thereof.

In yet a further embodiment, the corneal drug delivery implant is used for gene delivery with viral or non-viral antibody coated nanoparticles conjugated with DNA, RNA, or siRNA, and/or CRISPR/cas9 mediated homology-independent targeted integration (HITI) or homology directed repair (HDR) to modify the genetic components of various structures of the eye.

In yet a further embodiment, the corneal drug delivery implant is used for gene delivery with non-viral antibody coated or functionalized nanoparticles conjugated with cell penetrating agents and other medications, DNA, RNA, or siRNA, and/or CRISPR/cas9 mediated Homology-independent targeted integration (HITI) or homology directed repair (HDR).

In still a further embodiment, the medication of the corneal drug delivery implant or implants (if more than one implant is provided) comprises one or more medications selected from the group consisting of anti-inflammatory agents, Dexamethasone, NSAIDS, Anti IL-17, Anti IL-6, other Anti-ILs, antibiotics, fluoroquinolones, macrolides, cephalosporin A, vancomycin, aminoglycosides, penicillin and its derivatives, anti-virals, ganciclovir, valcyclovir, anti-fungals, amphotericine B, anti-VEGFs, Avastin, lucentis, Aflilbercept, anti-parasitics, immune-suppressants, Mycophenolic acid, cyclosporine, anti-proliferative agents, anti-metabolite agents, anti-glaucoma medications, Rho inhibitors, Wnt inhibitors, and combinations thereof.

In yet a further embodiment, the corneal drug delivery implant or implants (if more than one implant is provided) comprises a plurality of stem cells, the plurality of stem cells selected from the group consisting of embryonic stem cells, ciliary hormone producing cells, neuronal stem cells, glial stem cells, Mesnchymal stem cells, trabecular meshwork stem cells, limbal stem cells, skin stem cells, and combinations thereof; and the plurality of stem cells are provided in a biocompatible fluid that permits nutrition to reach the plurality of stem cells in the corneal drug delivery implant where the stem cells are immortalized to produce one or more medications or growth factors.

In still a further embodiment, the corneal drug delivery implant comprises a tubular body portion with a circular sidewall and oppositely disposed ends, the circular sidewall of the tubular body portion comprising a plurality of holes that are sufficiently sized so as to permit the stem cells to escape from corneal drug delivery implant and to enter the tissue surrounding the tubular body portion of the corneal drug delivery implant and tissue beyond the tubular body portion of the corneal drug delivery implant.

In yet a further embodiment, the medication of the corneal drug delivery implant or implants (if more than one implant is provided) comprises one or more medications selected from the group consisting of immunosuppressive agents, calcineurin inhibitors, mycophenolic acid, tacrolimus, siraliums, steroids, MPP inhibitors, NSAIDs, antimetabolytes, polycolonal antibodies, monocolonal antibodies, TNF inhibitors, Rho inhibitors, Wnt inhibitors, Fingolimod, Brimonidine, antibiotics, intraocular pressure (IOP) lowering agents, pilocarpine, prostaglandin analogues, anti-virals, anti-VEGFs, biologics, neuroprotective medications, and combinations thereof.

In a still further embodiment, the method further comprises the step of: (v) refilling the corneal drug delivery implant in the pocket with the medication by using a needle to inject the medication into the corneal drug delivery implant.

In yet a further embodiment, the corneal drug delivery implant is formed from polymeric nanoparticles, micelles, liposomes, dendrimers, or combinations thereof.

In a still further embodiment, in addition to implanting the corneal drug delivery implant with the one or more medications into the pocket, the method further comprises implanting one or more additional implants in the cornea, the one or more additional implants selected from the group consisting of: (i) a biopsy implant for taking liquid biopsies from a portion of the eye, (ii) a stem cell implant for delivering therapeutic stem cells to the eye of the patient, (iii) a gene therapy implant for delivering therapeutic genes to the eye of the patient for treating degenerative or genetic diseases, (iv) a pressure sensor implant for measuring the intraocular pressure of the eye of the patient, and (v) any combination including one or all of the additional implants.

In accordance with one or more other embodiments of the present invention, there is provided a method of implanting a drug delivery implant in a body portion of a patient. The method comprising the steps of: (i) forming a pocket in the body portion of the patient so as to gain access to tissue surrounding the pocket; (ii) after the pocket in the body portion of the patient has been formed, applying a photosensitizer inside the pocket so that the photosensitizer permeates at least a portion of the tissue surrounding the pocket, the photosensitizer facilitating cross-linking of the tissue surrounding the pocket; (iii) irradiating the body portion of the patient so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket; and (iv) before or after the portion of the tissue surrounding the pocket has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, inserting a drug delivery implant into the pocket, the drug delivery implant configured to release one or more medications into the body portion the patient.

In a further embodiment of the present invention, the step of inserting the drug delivery implant into the pocket comprises implanting the drug delivery implant in one or more eye locations selected from the group consisting of under the conjunctiva, under the sclera, over the sclera in the choroid, in the retina, and in the sub-retinal space.

In yet a further embodiment, the step of inserting the drug delivery implant into the pocket comprises implanting the drug delivery implant in a wall of a vitreous cavity of an eye of the patient with one end of the drug delivery implant being open to the vitreous cavity so as to permit the release of medication into the vitreous cavity.

In accordance with yet one or more other embodiments of the present invention, there is provided a corneal drug delivery implant that includes an implant body portion, the implant body portion having a shape selected from the group consisting of a rod shape, a C-shape, a semi-circular shape, a doughnut shape, or a rectangular flat tube shape, the implant body portion coated with a biocompatible material, the biocompatible material selected from the group consisting of collagen, elastin, polyethylene glycol, biotin, streptavidin, and combinations thereof; and a medication disposed within the implant body portion, the medication comprising one or more medications selected from the group consisting of anti-inflammatory agents, Dexamethasone, NSAIDS, Anti IL-17, Anti IL-6, other Anti-ILs, antibiotics, fluoroquinolones, macrolides, cephalosporin A, vancomycin, aminoglycosides, penicillin and its derivatives, anti-virals, ganciclovir, valcyclovir, anti-fungals, amphotericine B, anti-VEGFs, Avastin, lucentis, Aflilbercept, anti-parasitics, immune-suppressants, Mycophenolic acid, cyclosporine A, anti-proliferative agents, anti-metabolite agents, anti-glaucoma medications, Rho inhibitors, Wnt inhibitors, and combinations thereof.

In a further embodiment of the present invention, the corneal drug delivery implant further comprises a needle configured to fluidly couple the corneal drug delivery implant with a fluid in an interior chamber of the eye.

In yet a further embodiment, the corneal drug delivery implant or implants (if more than one implant is provided) is implanted after stromal refractive surgery under the flap created by the femtosecond laser close or away from the peripheral flap to deliver medication, such as antibiotic anti-virals, ganciclovir, valcyclovir, anti-fungals, amphotericine B, anti-VEGFs, Avastin, lucentis, Aflilbercept, anti-parasitics, immune-suppressants, Mycophenolic acid, cyclosporine A, anti-proliferative agents, anti-metabolite agents, anti-glaucoma medications, Rho inhibitors, Wnt inhibitors, and combinations thereof to the cornea.

It is to be understood that the foregoing general description and the following detailed description of the present invention are merely exemplary and explanatory in nature. As such, the foregoing general description and the following detailed description of the invention should not be construed to limit the scope of the appended claims in any sense.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

The invention will now be described, by way of example, with reference to the accompanying drawings, in which:

FIG. 1A is a partial side cross-sectional view of an eye having a scarred cornea, wherein substantially the entire thickness of the cornea is scarred;

FIG. 1B is a partial side cross-sectional view of a donor cornea undergoing cross-linking;

FIG. 1C is a partial side cross-sectional view of the eye of FIG. 1A, wherein the scarred cornea is shown being removed;

FIG. 1D is a partial side cross-sectional view of the eye of FIG. 1A, wherein the cross-linked donor cornea is shown being implanted in the location previously occupied by the scarred cornea;

FIG. 2A is a partial side cross-sectional view of an eye having internal corneal scar tissue;

FIG. 2B is a partial side cross-sectional view of the eye of FIG. 2A, wherein the scarred corneal tissue has been externally removed from the eye;

FIG. 2C is a partial side cross-sectional view of the eye of FIG. 2A, wherein a cross-linked donor cornea is shown being implanted in the location previously occupied by the scarred corneal tissue;

FIG. 3A is a partial side cross-sectional view of an eye having internal corneal scar tissue;

FIG. 3B is a partial side cross-sectional view of the eye of FIG. 3A, wherein the scarred corneal tissue is shown being internally removed from the eye;

FIG. 3C is a partial side cross-sectional view of the eye of FIG. 3A, wherein a cross-linked donor cornea is shown being implanted in the location previously occupied by the scarred corneal tissue;

FIG. 4A is a partial side cross-sectional view of an eye having a T-shaped corneal scar and/or diseased tissue portion;

FIG. 4B is another partial side cross-sectional view of a donor cornea undergoing cross-linking;

FIG. 4C is a partial side cross-sectional view illustrating a T-shaped portion of the cross-linked donor cornea being cut out from a remainder of the donor cornea;

FIG. 4D is a partial side cross-sectional view of the eye of FIG. 4A, wherein the T-shaped scarred and/or diseased portion of corneal tissue has been removed from the eye;

FIG. 4E is a partial side cross-sectional view of the eye of FIG. 4A, wherein the cross-linked T-shaped donor cornea portion is shown being implanted in the location previously occupied by the scarred and/or diseased corneal tissue portion;

FIG. 5A illustrates an alternative configuration for the cross-linked donor cornea implant, wherein the donor cornea implant has a dumbbell shape;

FIG. 5B illustrates another alternative configuration for the cross-linked donor cornea implant, wherein the donor cornea implant has a reversed or upside down T-shape;

FIG. 6A is a side cross-sectional view of a host eye prior to an transplant procedure;

FIG. 6B is another side cross-sectional view of the host eye of FIG. 6A, which illustrates a creation of a corneal pocket therein;

FIG. 6C is another side cross-sectional view of the host eye of FIG. 6A, which illustrates an implantation of the cross-linked lamellar lenslet into the host eye;

FIG. 7A is a partial side cross-sectional view of a donor cornea being cross-linked prior to being shaped for use in a transplant procedure;

FIG. 7B is another partial side cross-sectional view of the donor cornea of FIG. 7A, which illustrates the cutting of a cross-linked lamellar lenslet from a remainder of the cross-lined donor cornea;

FIG. 7C is a side cross-sectional view of the cross-linked lamellar lenslet after it has been appropriately shaped and removed from the donor cornea of FIGS. 7A and 7B;

FIG. 8 is a partial side cross-sectional view illustrating the formation of a two-dimensional cut into a cornea of an eye, according to another embodiment of the invention;

FIG. 9 is another partial side cross-sectional view of the eye of FIG. 8, which illustrates the creation of a three-dimensional pocket in the cornea of the eye;

FIG. 10 is yet another partial side cross-sectional view of the eye of FIG. 8, which illustrates the injection of a photosensitizer into the three-dimensional pocket in the cornea of the eye;

FIG. 11A is still another partial side cross-sectional view of the eye of FIG. 8, which illustrates the irradiation of the stromal tissue surrounding the three-dimensional pocket of the eye using ultraviolet radiation delivered from outside of the cornea;

FIG. 11B is yet another partial side cross-sectional view of the eye of FIG. 8, which illustrates the irradiation of the stromal tissue surrounding the three-dimensional pocket of the eye using a fiber optic delivering ultraviolet radiation inside the three-dimensional pocket, according to an alternative embodiment of the invention;

FIG. 12 is still another partial side cross-sectional view of the eye of FIG. 8, which illustrates a lens implant inserted into the pocket so as to change the refractive properties of the eye;

FIG. 13 is yet another partial side cross-sectional view of the eye of FIG. 8, which illustrates the reinjection of a photosensitizer into the three-dimensional pocket with the lens implant disposed therein so that the cross-linking procedure may be repeated;

FIG. 14 is still another partial side cross-sectional view of the eye of FIG. 8, which illustrates the re-irradiation of the stromal tissue surrounding the three-dimensional pocket of the eye during the repetition of the cross-linking procedure;

FIG. 15 is a side cross-sectional view illustrating the creation of a lens implant from an organic block of polymer using a excimer laser;

FIG. 16 is a side cross-sectional view illustrating the cutting of a lens implant from an organic block of polymer using a femtosecond laser;

FIG. 17 is a side cross-sectional view illustrating a lens implant that has been formed using a three-dimensional printing technique or a molding technique;

FIG. 18 is a front view of a cornea of an eye, according to yet another embodiment of the invention;

FIG. 19 is another front view of the cornea of the eye of FIG. 18, wherein a square-shaped intrastromal pocket has been formed in the cornea of the eye;

FIG. 20 is yet another front view of the cornea of the eye of FIG. 18, wherein a circular three-dimensional portion of tissue having a first diameter has been removed from the area within the square-shaped intrastromal pocket;

FIG. 21 is still another front view of the cornea of the eye of FIG. 18, wherein a circular three-dimensional portion of tissue having second diameter has been removed from the area within the square-shaped intrastromal pocket, the second diameter of the circular three-dimensional portion of tissue in FIG. 21 being larger than the first diameter of the circular three-dimensional portion of tissue in FIG. 20;

FIG. 22 is yet another front view of the cornea of the eye of FIG. 18, wherein a circular lens implant has been implanted in the area where the circular three-dimensional portion of tissue has been removed, and wherein a photosensitizer is being injected into the pocket in the cornea of the eye;

FIG. 23 is still another front view of the cornea of the eye of FIG. 18, wherein the circular lens implant is shown in the area where the circular three-dimensional portion of tissue was removed;

FIG. 24 is a side cross-sectional view illustrating an eye with a cataract, according to still another embodiment of the invention;

FIG. 25 is another side cross-sectional view of the eye of FIG. 24, which illustrates the breaking apart of the natural lens into lens fragments using a laser;

FIG. 26 is yet another side cross-sectional view of the eye of FIG. 24, which illustrates the irrigation and aspiration of the lens fragments of the natural lens using a probe;

FIG. 27 is still another side cross-sectional view of the eye of FIG. 24, which illustrates the application of a photosensitizer to the capsular bag of the eye after the cataract has been removed;

FIG. 28 is yet another side cross-sectional view of the eye of FIG. 24, which illustrates the irradiation of the capsular bag of the eye using a fiber optic so as to activate cross-linkers in the capsular bag;

FIG. 29 is still another side cross-sectional view of the eye of FIG. 24, which illustrates the injection a transparent polymer into the lens capsule of the eye in order to form an accommodative intraocular lens for replacing the cortex and nucleus of the natural lens that was removed from the eye;

FIG. 30 is a side cross-sectional view illustrating an eye with a cataract, according to yet another embodiment of the invention;

FIG. 31 is another side cross-sectional view of the eye of FIG. 30, which illustrates the application of a photosensitizer to a posterior portion of the capsular bag of the eye after the cataract has been removed;

FIG. 32 is yet another side cross-sectional view of the eye of FIG. 30, which illustrates the irradiation of the posterior portion of the capsular bag of the eye so as to activate cross-linkers in the posterior portion of the capsular bag;

FIG. 33 is still another side cross-sectional view of the eye of FIG. 30, which illustrates the capsular bag of the eye after the removal of the cataract and the placement of an intraocular lens in the capsular bag;

FIG. 34 is a yet another side cross-sectional view of the eye of FIG. 30, which illustrates the intraocular lens in the capsular bag of the eye prior to glaucoma surgery being performed on the eye;

FIG. 35 is still another side cross-sectional view of the eye of FIG. 30, which illustrates the insertion of a stent through an anterior chamber of the eye and into the subconjunctival space;

FIG. 36 is a partial, enlarged view illustrating the insertion of the stent in FIG. 35 (Detail “A”);

FIG. 37 is yet another side cross-sectional view of the eye of FIG. 30, which illustrates the application of a photo sensitizer to an anterior chamber of the eye so that the photosensitizer is capable of diffusing out of the stent and into the subconjunctival space;

FIG. 38 is still another side cross-sectional view of the eye of FIG. 30, which illustrates the irradiation of the subconjunctival space so as to activate cross-linkers and prevent fibrosis around the stent outflow;

FIG. 39 is yet another side cross-sectional view of the eye of FIG. 30, which illustrates the application of a photo sensitizer to the anterior chamber of the eye and the irradiation of the subconjunctival space so as to activate cross-linkers and prevent fibrosis around a shunt or opening in the eye wall;

FIG. 40 is a partial, enlarged view illustrating the application of the photosensitizer and the irradiation of the space around the shunt or opening in the eye wall of FIG. 39 (Detail “B”);

FIG. 41 is still another side cross-sectional view of the eye of FIG. 30, which illustrates the application of a photo sensitizer to the anterior chamber of the eye and the irradiation of the suprachoroidal space so as to activate cross-linkers and prevent fibrosis around a stent in the suprachoroidal space;

FIG. 42 is a perspective view illustrating a glaucoma stent having a coating provided thereon, according to an embodiment of the invention;

FIG. 43 is a side cross-sectional view illustrating a syringe used for the implantation of the stent of FIG. 42, according to an embodiment of the invention;

FIG. 44 is a side cross-sectional view of an eye, which illustrates the application of liquid collagen to the subconjunctival space, according to another embodiment of the invention;

FIG. 45 is another side cross-sectional view of the eye of FIG. 44, which illustrates the application of a photosensitizer after the implantation of the glaucoma stent of FIG. 42 in the eye;

FIG. 46 is yet another side cross-sectional view of the eye of FIG. 44, which illustrates the irradiation of the glaucoma stent and the surrounding areas in the eye so as to activate cross-linkers and prevent fibrosis;

FIG. 47 is a partial side cross-sectional view illustrating the formation of an incision into a peripheral portion of a cornea of an eye so as to create a pocket for receiving a corneal intraocular pressure sensor, according to another embodiment of the invention;

FIG. 48 is another partial side cross-sectional view of the eye of FIG. 47, which illustrates the injection of a photosensitizer into the pocket in the peripheral portion of the cornea of the eye;

FIG. 49 is yet another partial side cross-sectional view of the eye of FIG. 47, which illustrates the irradiation of the stromal tissue surrounding the pocket in the peripheral portion of the cornea of the eye using ultraviolet radiation delivered from outside of the cornea;

FIG. 50 is still another partial side cross-sectional view of the eye of FIG. 47, which illustrates the irradiation of the stromal tissue surrounding the pocket in the peripheral portion of the cornea of the eye using a fiber optic delivering ultraviolet radiation inside the pocket, according to an alternative embodiment of the invention;

FIG. 51 is a front view of the eye of FIG. 47, which illustrates the components of a corneal intraocular pressure sensor disposed in the pocket in the peripheral portion of the cornea of the eye;

FIG. 52 is still another partial side cross-sectional view of the eye of FIG. 47, which illustrates the peripheral cross-linked corneal pocket with the components of the corneal intraocular pressure sensor disposed therein;

FIG. 53 is a partial, enlarged side cross-sectional view of the eye of FIG. 52 (Detail “C”), which illustrates the needle of the corneal intraocular pressure sensor extending into the anterior chamber of the eye.

FIG. 54A illustrates a first exemplary shape for the drug delivery implant described herein, which is in the form of a rod-shaped implant;

FIG. 54B illustrates a second exemplary shape for the drug delivery implant described herein, which is in the form of a curved implant;

FIG. 54C illustrates a third exemplary shape for the drug delivery implant described herein, which is in the form of a two-part semi-circular implant;

FIG. 54D illustrates a fourth exemplary shape for the drug delivery implant described herein, which is in the form of a one-part semi-circular implant;

FIG. 55 illustrates an exemplary coated drug delivery implant, wherein the drug delivery implant is coated with a polymer and a photosensitizer;

FIG. 56A illustrates a first exemplary form of the drug delivery implant described herein, which is in the form of a solid tubular implant;

FIG. 56B illustrates a second exemplary form of the drug delivery implant described herein, which is in the form of a porous tubular implant;

FIG. 56C illustrates a third exemplary form of the drug delivery implant described herein, which is in the form of a tubular implant with open ends;

FIG. 57 illustrates another exemplary form of the drug delivery implant described herein, wherein the implant is tubular-shaped with holes formed in the side thereof;

FIG. 58 illustrates yet another exemplary form of the drug delivery implant that is similar to that which is depicted in FIG. 57, except that the tubular-shaped implant of FIG. 58 has larger-sized holes formed in the side thereof;

FIG. 59 illustrates still another exemplary form of the drug delivery implant described herein, wherein the implant is in the form of a rectangular flat tube;

FIG. 60 illustrates yet another exemplary form of the drug delivery implant described herein, wherein the implant is in the form of a semi-solid or silicone tubular implant with one closed end and one open end;

FIG. 61 illustrates still another exemplary form of the drug delivery implant described herein, wherein the implant is in the form of a rectangular tube that is refillable by injection;

FIG. 62 illustrates yet another exemplary form of the drug delivery implant described herein, wherein the tubular implant comprises a needle for tissue penetration and the tubular implant is capable of being penetrating by a needle for taking liquid biopsies;

FIG. 63A is a front view of a cornea of an eye illustrating a two-part semi-circular drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea that is spaced apart from the central visual axis of the eye so as not to obstruct the central portion of the eye;

FIG. 63B is a partial side cross-sectional view of the eye of FIG. 63A illustrating the two-part semi-circular drug delivery implant disposed in the cross-linked pocket in the peripheral portion of the cornea;

FIG. 64A is a front view of a cornea of an eye illustrating a generally linear drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea that is spaced apart from the central visual axis of the eye so as not to obstruct the central portion of the eye;

FIG. 64B is a partial side cross-sectional view of the eye of FIG. 64A illustrating the generally linear drug delivery implant disposed in the cross-linked pocket in the peripheral portion of the cornea;

FIG. 65A is a front view of a cornea of an eye illustrating a tubular drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea, wherein the implant comprises a needle fluidly coupling the implant to the anterior chamber of the eye;

FIG. 65B is a partial side cross-sectional view of the eye of FIG. 65A illustrating the tubular drug delivery implant with the needle extending into the anterior chamber of the eye;

FIG. 66A is a front view of a cornea of an eye illustrating a pupil, cornea, sclera, and limbus of the eye;

FIG. 66B is a partial side cross-sectional view of the eye of FIG. 66A illustrating an anterior chamber, iris, and lens of the eye;

FIG. 67A is a front view of a cornea of an eye illustrating a one-part semi-circular drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea;

FIG. 67B is a partial side cross-sectional view of the eye of FIG. 67A illustrating the one-part semi-circular drug delivery implant disposed in the cross-linked pocket in the peripheral portion of the cornea;

FIG. 68A is a front view of a cornea of an eye illustrating a doughnut-shaped drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea;

FIG. 68B is a partial side cross-sectional view of the eye of FIG. 68A illustrating the doughnut-shaped drug delivery implant disposed in the cross-linked pocket in the peripheral portion of the cornea;

FIG. 69A is a front view of a cornea of an eye illustrating a generally linear drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea;

FIG. 69B is a partial side cross-sectional view of the eye of FIG. 69A illustrating the generally linear drug delivery implant disposed in the cross-linked pocket in the peripheral portion of the cornea;

FIG. 70A is a front view of a cornea of an eye illustrating a drug delivery implant disposed in a cross-linked pocket in the peripheral portion of the cornea, wherein the implant comprises a needle fluidly coupling the implant to the anterior chamber of the eye; and

FIG. 70B is a partial side cross-sectional view of the eye of FIG. 70A illustrating the tubular drug delivery implant with the needle extending into the anterior chamber of the eye with the aqueous fluid of the eye.

Throughout the figures, the same elements are always denoted using the same reference characters so that, as a general rule, they will only be described once.

DETAILED DESCRIPTION OF EMBODIMENTS OF THE INVENTION

A first illustrative embodiment of a corneal transplant procedure with a cross-linked cornea is shown in FIGS. 1A-1D. The corneal transplant procedure illustrated in FIGS. 1A-1D involves full corneal replacement of the scarred or diseased cornea by the donor cornea. In other words, FIGS. 1A-1D illustrate a penetrating keratoplasty procedure wherein the full thickness of the scarred or diseased cornea is replaced with a cross-linked donor cornea (i.e., a full-thickness corneal transplant).

Referring initially to FIG. 1A, it can be seen that substantially the entire thickness of the cornea 16 of the eye 10 is scarred and/or diseased (i.e., scarred, diseased, or scarred and diseased). FIG. 1A also illustrates the lens 12 and iris 14 of the eye 10, which are located posteriorly of the cornea 16. In this embodiment, it is necessary to replace substantially the entire thickness of the cornea 16 with a donor cornea.

In FIG. 1B, the cross-linking 18 of the clear donor cornea 20 is diagrammatically illustrated. As depicted in FIG. 1B, only the front portion 20 a of the donor cornea 20 is cross-linked. That is, the cross-linking does not extend all the way to the rear portion 20 b of the donor cornea 20. It is to be understood that the cross-linking 18 of the donor cornea 20 may also be done after implanting the donor cornea into the eye of the patient, rather than before implantation as shown in the illustrative example of FIGS. 1A-1D. Also, it is to be understood that all or just a part of the donor cornea 20 may be cross-linked.

In the illustrative embodiments described herein (i.e., as depicted in FIGS. 1A-1D, 2A-2C, and 3A-3C), the cross-linking of the clear donor cornea may comprise the steps of: (i) applying a photosensitizer to the donor cornea, the photosensitizer facilitating cross-linking of the donor cornea; and (ii) irradiating the donor cornea with ultraviolet light so as to activate cross-linkers in the donor cornea and thereby strengthen the donor cornea. The photosensitizer may comprise riboflavin or a solution comprising a liquid suspension having nanoparticles of riboflavin. The cross-linker may have between about 0.1% Riboflavin to about 100% Riboflavin or any other suitable range or specific percentage therein. The ultraviolet radiation or rays used to irradiate the donor cornea may be between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). The radiation is preferably about 3 mW or more as needed and emanates from a laser source at about a 3 cm distance from the donor cornea for about 30 minutes or less. The time of the exposure can vary depending on the light intensity, focus, and the concentration of riboflavin. However, the ultraviolet radiation can be applied at any suitable distance, time or wavelength. Preferably, cross-linking the donor cornea does not significantly change the refractive power of the donor cornea; however, if desired, cross-linking can change the refractive power of the donor cornea to any suitable degree.

In addition to Riboflavin, other suitable cross linking agents are low carbon carbohydrates, such as pentose sugar (e.g., ribose) or hexose sugar (e.g., glucose), or complex carbohydrates. Other crosslinking agents may include Transaminidases, transglutaminases or a naturally-derived cross-linker named malic acid derivative (MAD) concentrations higher than 30 mM, commercially available cross-linkers such as 1-ethyl-3-(3(′-dimethylaminopropyl) carbodiimide (EDC), or ethyl-3(3-dimethylamino) propyl carbodiimide (EDC), etc. The cross-linking may also be done postoperatively by the application of other crosslinking agents, such as Triglycidylamine (TGA) synthesized via reacting epichlorhydrin and a carbodiimide, or the oxidized glycogen hexoses. The ribose, glucose and similar agents may penetrate the cornea easily using drops, gel, or the slow release mechanisms, nanoparticle, microspares, liposome sets. In addition, the crosslinkers may be delivered with Mucoadhesives.

In one or more embodiments, all or part of the donor cornea is cross-linked. Also, in one or more embodiments, a very high concentration of Riboflavin may be used because the in vitro cross-linking process may be stopped whenever needed prior to the transplantation of the donor cornea in the host eye. In addition, the power of the ultraviolet (UV) laser may also be increased so as to cross-link the tissue of the donor cornea faster. The use of a high concentration of Riboflavin, and the increasing of the ultraviolet (UV) laser power, are not possible during an in vivo cross-linking procedure because the aim of such an in vivo procedure is to protect the cells of the host cornea. Also, the in vivo process cannot be controlled as efficiently as in the vitro crosslinking of the corneal transplant.

In one or more embodiments, the donor cornea may be extracted from a human cadaver, or the cornea may be reconstructed as known in tissue engineering in vitro and three-dimensionally (3D) printed. Cross-linking of a culture-grown cornea eliminates the cellular structure inside the cornea. If needed again, the healthy corneal endothelium of the patient may be grown in vitro for these tissues by placing them on the concave surface of the cornea and encouraging their growth under laboratory control conditions prior to the transplantation.

In the embodiments where the donor cornea is tissue culture grown, the cornea may be formed from mesenchymal fibroblast stem cells, embryonic stem cells, or cells derived from epithelial stem cells extracted from the same patient, or a mixture of these cells. Using known tissue culture techniques, the cells may produce a transparent corneal stroma. This culture-grown corneal stroma will not have a corneal epithelium or a corneal endothelium. Thus, it eliminates the complexity of developing a full thickness cornea in the tissue culture. This stromal transplant may be used as a lamellar or partial thickness replacement of the existing host cornea. This transplant may also be used to augment or add to the thickness of the host cornea. This transparent corneal stroma may be transplanted either prior to, or after being cross-linked using various cross-linking methods.

In one or more embodiments, the cross-linked donor cornea may be sized and precisely cut with a femtosecond laser to the desired shape and curvature to replace the removed host cornea so that the refractive errors of the recipient are also automatically corrected with the cross-linked cornea.

Now, referring to FIG. 1C, it can be seen that the scarred and/or diseased cornea 16 is shown being removed from the eye 10. The scarred and/or diseased cornea 16 may be removed from the eye 10 by using various suitable means, such as mechanical means or cutting using a laser. When mechanical means are used to remove the scarred and/or diseased cornea 16 from the eye 10, the scarred and/or diseased cornea 16 may initially be cut away or dissected from the remainder of the eye 10 using a sharp mechanical instrument (e.g., a surgical micro-knife, a needle, a sharp spatula, a pair of micro-scissors), and then subsequently removed or extracted with a pair of micro-forceps. When laser cutting is used to remove the scarred and/or diseased cornea 16 from the eye 10, the scarred and/or diseased cornea 16 may be cut away using a suitable laser, such as a femtosecond laser. Also, in some embodiments, the mechanical means for cutting and extraction (e.g., the surgical micro-knife and/or pair of micro-scissors) may be used in combination with the laser means (e.g., the femtosecond laser).

In one or more embodiments, the donor cornea may be shaped and cut with the femtosecond laser prior to the cross-linking thereof so as to replace part or all of the recipient cornea which is cut with the femtosecond laser. In these one or more embodiments, the entire donor and host cornea together may be cross-linked with Riboflavin and UV radiation. These procedures may also be performed on a culture-grown transplant cornea.

Then, as shown in FIG. 1D, after the scarred and/or diseased cornea 16 has been removed from the eye 10, the cross-linked donor cornea 20 is implanted into the eye 10 of the patient in the location previously occupied by the scarred and/or diseased cornea 16. After implantation of the cross-linked donor cornea 20, sutures or a suitable adhesive may be utilized to secure the cross-linked donor cornea 20 in place on the eye 10. When sutures are used for holding the donor cornea 20 in place, the sutures may comprise nylon sutures, steel sutures, or another suitable type of non-absorbable suture. When the cornea 16 is subsequently ablated after the implantation of the donor cornea, as will be described hereinafter, additional sutures may be required after ablation.

In one or more embodiments, a biodegradable adhesive is used in a corneal transplantation procedure with the cross-linked donor cornea 20 described above, or with a non-cross-linked corneal transplant. In these one or more embodiments, the biodegradable adhesive obviates the need for a suture in the corneal transplant procedure. Sutures generally distort the surface of the cornea and can produce an optically unacceptable corneal surface. Also, the use of the biodegradable adhesive obviates the need for glues requiring exothermic energy. Glues that use an exothermic effect, such as Fibronectin, need thermal energy to activate their adhesive properties. This thermal energy, such as that delivered by a high-powered laser, produces sufficient heat to coagulate the Fibronectin and the tissue that it contacts. Any thermal effect on the cornea produces: (i) corneal opacity, (ii) tissue contraction, and (iii) distortion of the optical surface of the cornea. The tissue adhesion created by these glues, including Fibronectin or fibrinogen, is flimsy and cannot withstand the intraocular pressure of the eye.

In fact, sutures are superior to these types of adhesives because the wound becomes immediately strong with sutures, thereby supporting the normal intraocular pressure of between 18 and 35 mmHg. In contrast to the use of a suture in which distortion that is caused by suture placement can be managed by cutting and removing the suture, the distortion caused by the coagulated corneal tissue cannot be corrected.

Other glues, such as cyanoacrylate, become immediately solid after coming into contact with the tissue or water. These glues produce a rock-hard polymer, the shape of which cannot be controlled after administration. Also, the surface of the polymer created by these glues is not smooth. Thus, the eyelid will rub on this uneven surface, and the uneven surface scratches the undersurface of the eyelid when the eyelid moves over it. In addition, the cyanoacrylate is not biodegradable or biocompatible. As such, it causes an inflammatory response if applied to the tissue, thereby causing undesirable cell migration and vascularization of the cornea.

Thus, by using a biocompatible and absorbable acrylate or other biodegradable glues that do not need exothermic energy for the process of adhesion (i.e., like fibronectin or fibrinogen), one is able to maintain the integrity of the smooth corneal surface. In one or more embodiments, the biocompatible and biodegradable adhesive may be painted only at the edges of the transplant prior to placing it in the host or diseased cornea. In these embodiments, the biocompatible and biodegradable adhesive only comes into contact with the host tissue at the desired predetermined surface to create a strong adhesion. The adhesion may last a few hours to several months depending on the composition of the molecule chosen and the concentration of the active component.

Other suitable biodegradable adhesives or glues that may be used in conjunction with the transplant include combinations of gallic acid, gallic tannic acid, Chitosan, gelatin, polyphenyl compound, Tannic Acid (N-isopropylacrylamide (PNIPAM), and/or Poly(N-vinylpyrrolidone) with polyethylene glycol (PEG). That is, polyethylene glycol (PEG) may be mixed with any one or plurality of gallic acid, gallic tannic acid, Chitosan, gelatin, polyphenyl compound, Tannic Acid (N-isopropylacrylamide (PNIPAM), and Poly(N-vinylpyrrolidone), so as to form a molecular glue. These adhesives are suitable for the use on the cornea because they create a tight wound that prevents leakage from the corneal wound and maintain the normal intraocular pressure shortly after their application and also do not distort the wound by causing traction on the tissue.

In addition, other suitable biodegradable adhesives or glues, which may need an external source of energy, that are able to be used in conjunction with the transplant include combinations of riboflavin, lactoflavin, gallic acid, gallic tannic acid, Chitosan, gelatin, polyphenyl compound, Tannic Acid (N-isopropylacrylamide (PNIPAM), dopamine, and/or Poly(N-vinylpyrrolidone) with polyethylene glycol (PEG). That is, polyethylene glycol (PEG) may be mixed with any one or plurality of riboflavin, lactoflavin, tannic acid, dopamine, gallic tannic acid, Chitosan, gelatin, polyphenyl compound, Tannic Acid (N-isopropylacrylamide (PNIPAM), and Poly(N-vinylpyrrolidone), so as to form a molecular glue. These adhesives are also suitable for the use on the cornea because they create a tight wound that prevents leakage from the corneal wound and maintain the normal intraocular pressure shortly after their application and also do not distort the wound by causing traction on the tissue.

In one or more embodiments, the donor cornea may be temporarily sutured to the host cornea by only a few single sutures to the host cornea. Then, the sutures may be removed immediately after donor cornea is fixed to the host cornea with a suitable adhesive.

A second illustrative embodiment of a corneal transplant procedure with a cross-linked cornea is shown in FIGS. 2A-2C. Unlike the first embodiment described above, the corneal transplant procedure illustrated in FIGS. 2A-2C does not involve full corneal replacement of the scarred or diseased cornea by the donor cornea. Rather, FIGS. 2A-2C illustrate a lamellar keratoplasty procedure wherein only a portion of the cornea 16′ of the eye 10′ contains scarred and/or diseased tissue (i.e., a full-thickness corneal section is not removed). In the procedure of FIGS. 2A-2C, an internal scarred and/or diseased portion 16 a′ of the cornea 16′ is externally removed from the eye 10′ of a patient.

Referring initially to FIG. 2A, it can be seen that only an internal portion 16 a′ of the cornea 16′ is scarred and/or diseased. As such, in this embodiment, it is not necessary to replace the entire thickness of the cornea 16 with a donor cornea as was described above in conjunction with FIGS. 1A-1D, but rather just a portion of the cornea 16′.

Next, referring to FIG. 2B, it can be seen that the scarred and/or diseased portion 16 a′ has been externally removed from the cornea 16′ of the eye 10′ such that the cornea 16′ comprises a cavity 19 disposed therein for receiving the donor cornea. Because an external approach was utilized for removing the scarred and/or diseased portion 16 a′ of the cornea 16′, the cavity 19 comprises a notch-like void in the outside or anterior surface of the cornea 16′. As described above for the first embodiment, the scarred and/or diseased corneal portion 16 a′ may be removed from the remainder of the cornea 16′ using various suitable means, such as mechanical means or the laser cutting means (e.g., femtosecond laser) described above.

Finally, as shown in FIG. 2C, after the scarred and/or diseased portion 16 a′ has been removed from the remainder of the cornea 16′ of the eye 10′, the cross-linked donor cornea or cross-linked donor corneal portion 20′ is implanted into the eye 10′ of the patient in the location previously occupied by the scarred and/or diseased corneal portion 16 a′. As described above, after implantation of the cross-linked donor corneal portion 20′ into the eye 10′, sutures or a suitable adhesive (e.g., the biocompatible and biodegradable adhesive described above) may be utilized to secure the cross-linked donor corneal portion 20′ in place on the host cornea of the eye 10′.

After the cross-linked donor corneal portion 20′ is implanted into the eye 10′ of the patient, a portion of the cornea 16′ may be ablated so as to change the refractive properties of the eye (e.g., to give the patient perfect or near perfect refraction). The ablation of the portion of the cornea 16′ may be performed using a suitable laser 34, such as an excimer laser. The ablation by the laser causes the ablated tissue to essentially evaporate into the air. Also, the ablation of the portion of the cornea 16′ may be done intrastromally, as with LASIK (laser-assisted in situ keratomileusis), or on the surface of the cornea, as with PRK (photorefractive keratectomy). The ablation may be performed a predetermined time period after the corneal transplantation so as to enable the wound healing process of the recipient's cornea to be completed. It is to be understood that the ablation, which follows the corneal transplantation, may be performed in conjunction with any of the embodiments described herein.

It is also to be understood that, in some alternative embodiments, the ablation may be performed prior to the transplantation of the donor cornea, rather than after the transplantation of the donor cornea. For example, in one or more alternative embodiments, a lenticle may be precisely cut in the tissue of a culture-grown stroma of a donor cornea by using a femtosecond laser so that when implanted into the host cornea, it corrects the residual host eye's refractive error.

A third illustrative embodiment of a corneal transplant procedure with a cross-linked cornea is shown in FIGS. 3A-3C. Like the second embodiment described above, the corneal transplant procedure illustrated in FIGS. 3A-3C only involves replacing a scarred and/or diseased portion 16 a″ of the cornea 16″ with a donor corneal portion. Thus, similar to the second embodiment explained above, FIGS. 3A-3C illustrate a lamellar keratoplasty procedure wherein only a portion of the cornea 16″ of the eye 10″ contains scarred and/or diseased tissue (i.e., a full-thickness corneal section is not removed). Although, in the procedure of FIGS. 3A-3C, an internal scarred and/or diseased portion 16 a″ of the cornea 16″ is internally removed from the eye 10″ of a patient, rather than being externally removed as in the second embodiment of FIGS. 2A-2C.

Referring initially to FIG. 3A, it can be seen that only an internal portion 16 a″ of the cornea 16″ of the eye 10″ is scarred and/or diseased. As such, in this embodiment, like the preceding second embodiment, it is not necessary to replace the entire thickness of the cornea 16″ with a donor cornea, but rather just a portion of the cornea 16″.

Next, referring to FIG. 3B, it can be seen that the scarred and/or diseased portion 16 a″ is being internally removed from the remainder of the cornea 16″ using a pair of forceps 22 (i.e., mechanical means of removal are illustrated in FIG. 3B). Advantageously, because an internal approach is being utilized for removing the scarred and/or diseased portion 16 a″ of the cornea 16″, the cornea 16″ will not comprise the notch-like cavity 19 disposed in the outside or anterior surface of the cornea, which was described in conjunction with the preceding second embodiment. As described above for the first and second embodiments, the scarred and/or diseased corneal portion 16 a″ may be removed from the remainder of the cornea 16″ using other suitable alternative means, such as laser cutting techniques (e.g., using a femtosecond laser). Advantageously, the femtosecond laser is capable of cutting inside the tissue without involving the surface of the tissue. The cut part of the tissue can then be removed by other means (e.g., micro-forceps).

Finally, as shown in FIG. 3C, after the scarred and/or diseased corneal portion 16 a″ has been removed from the remainder of the cornea 16″ of the eye 10″, the cross-linked donor cornea or cross-linked donor corneal portion 20″ is implanted into the eye 10″ of the patient in the location previously occupied by the scarred and/or diseased corneal portion 16 a″. After implantation of the cross-linked donor corneal portion 20″, sutures or a suitable adhesive (e.g., the biocompatible and biodegradable adhesive described above) may be utilized to secure the cross-linked donor corneal portion 20″ in place on the host cornea of the eye 10″. Advantageously, the cross-linked donor corneal portion 20″, which is strengthened by the cross-linking performed thereon, reinforces the cornea 16″ and greatly reduces the likelihood of corneal graft rejection.

It is to be understood that the scarred and/or diseased corneal portion 16 a″ that is removed from the cornea 16″ may also be replaced with stroma stem cells or mesenchymal stem cells, which can be contained in a medium, and then injected in the internal cavity previously occupied by the scarred and/or diseased corneal tissue 16 a″.

In one or more embodiments, mesenchymal stem cells also may be injected inside the donor cornea before or after transplantation. In addition, in one or more embodiments, daily drops of a Rho Kinase inhibitor may be added to the host eye after the surgery. The use of a medication, such as a Rho Kinase inhibitor, with the stem cells will encourage stem cell proliferation.

A fourth illustrative embodiment of a corneal transplant procedure with a cross-linked cornea is shown in FIGS. 4A-4E. Like the second and third embodiments described above, the corneal transplant procedure illustrated in FIGS. 4A-4E only involves replacing a scarred and/or diseased portion 16 a′″ of the cornea 16′″ with a donor corneal portion. Thus, similar to the second and third embodiments explained above, FIGS. 4A-4E illustrate a lamellar keratoplasty procedure wherein only a portion of the cornea 16′″ of the eye 10′″ contains scarred and/or diseased tissue (i.e., a full-thickness corneal section is not removed). Although, in the procedure of FIGS. 4A-4E, a different-shaped scarred and/or diseased portion 16 a′″ of the cornea 16′″ is removed.

Referring initially to FIG. 4A, it can be seen that only a portion 16 a′″ of the cornea 16′″ having a T-shape or “top hut” shape is scarred and/or diseased. As such, in this embodiment, it is not necessary to replace the entire thickness of the cornea 16′″ with a donor cornea as was described above in conjunction with FIGS. 1A-1D, but rather just a portion 16 a′″ of the cornea 16′″. In this illustrative embodiment, the back side of the cornea 16′″ is maintained (see e.g., FIG. 4D).

In FIG. 4B, the cross-linking 18′ of the clear donor cornea 20′ is diagrammatically illustrated. As mentioned above, it is to be understood that all or just a part of the donor cornea 20′ may be cross-linked. Then, in FIG. 4C, it can be seen that a portion 20 a′ of the clear donor cornea 20′, which has a T-shape or “top hut” shape that matches the shape of the scarred and/or diseased portion 16 a′″ of the cornea 16′″, is cut out from the remainder of the clear donor cornea 20′ such that it has the necessary shape. In one or more embodiments, the portion 20 a′ may be cut from the clear donor cornea 20′ and appropriately shaped using a femtosecond laser. As shown in FIGS. 5A and 5B, other suitably shaped cross-linked corneal portions may be cut from the clear donor cornea 20′, such as a dumbbell-shaped corneal portion 20 a″ (see FIG. 5A) or a corneal portion 20 a′″ having a reversed T-shape or “reversed top hut” shape (see FIG. 5B), in order to accommodate correspondingly shaped scarred and/or diseased areas in the host cornea.

Next, referring to FIG. 4D, it can be seen that the scarred and/or diseased portion 16 a′″ having the T-shape or “top hut” shape has been removed from the cornea 16′″ of the eye 10′″ such that the cornea 16′″ comprises a cavity 19′ disposed therein for receiving the donor cornea. As described above for the first three embodiments, the scarred and/or diseased corneal portion 16 a′″ may be removed from the remainder of the cornea 16′″ using various suitable means, such as mechanical means or the laser cutting means (e.g., femtosecond laser) described above.

Finally, as shown in FIG. 4E, after the scarred and/or diseased portion 16 a′″ has been removed from the remainder of the cornea 16′″ of the eye 10′″, the cross-linked donor corneal portion 20 a′ is implanted into the eye 10′″ of the patient in the location previously occupied by the scarred and/or diseased corneal portion 16 a′″. Because the shape of the transplant corresponds to that of the removed portion 16 a′″ of the cornea 16′″, the transplant sits comfortably in its position in the host cornea. As described above, after implantation of the cross-linked donor corneal portion 20 a′ into the eye 10′″, sutures or a suitable adhesive (e.g., the biocompatible and biodegradable adhesive described above) may be utilized to secure the cross-linked donor corneal portion 20 a′ in place on the host cornea 16′″ of the eye 10″. For example, if a biocompatible and biodegradable adhesive is used to secure the cross-linked donor corneal portion 20 a′ in place in the cornea 16′″ of the eye 10′″, the edges of the donor corneal portion 20 a′ are coated with the biocompatible and biodegradable adhesive so as to give the transplant a reliable stability. In this case, it is desirable to have the attachment of the transplant maintained by the biocompatible and biodegradable adhesive for a period of months (i.e., it is desirable for the transplant to be secured in place by the biocompatible and biodegradable adhesive for as long as possible).

An illustrative embodiment of a corneal lenslet implantation procedure with a cross-linked cornea is shown in FIGS. 6A-6C and 7A-7C. Similar to the second, third, and fourth embodiments described above, FIGS. 6A-6C and 7A-7C illustrate a lamellar keratoplasty procedure wherein only a portion of the cornea 16″″ of the host eye 10″″ is removed during the procedure (i.e., a full-thickness corneal section is not removed). Although, the procedure of FIGS. 6A-6C and 7A-7C differs in several important respects from the above described procedures. In this embodiment, the corneal transplant is cross-linked in vitro. Then, using a femtosecond laser or an excimer laser, the surgeon carves out or ablates a three-dimensional (3D) corneal cross-linked augment from the donor cornea 20′″ that exactly compensates for the refractive error of the recipient of the transplant. That is, the corneal cross-linked augment or inlay may be cut to the desired shape using a femtosecond laser, or the inlay may be shaped in vitro using an excimer laser prior to its implantation in the cornea 16″″ of the host eye 10″″. After making an internal pocket 28 in the recipient cornea 16″″ of the host eye 10″″ with a femtosecond laser, the cross-linked transplant is folded and implanted in a predetermined fashion inside the host's corneal pocket 28 to provide stability to the eye 10″″ having keratoconus, keratoglobus, a thin cornea or abnormal corneal curvature, thereby preventing future corneal ectasia in this eye 10″″ and correcting its refractive errors. Advantageously, the procedure of this embodiment comprises a lamellar cross-linked corneal transplantation, which additionally results in simultaneous correction of the refractive error of the eye 10″″ of the patient. As used herein, the term “lenslet” refers to a lens implant configured to be implanted in a cornea of an eye. The lens implant may be formed from an organic material, a synthetic material, or a combination of organic and synthetic materials.

Now, with reference to FIGS. 6A-6C and 7A-7C, the illustrative embodiment will be described in further detail. The host eye 10″″ with lens 12′, cornea 16″″, and optic nerve 24 is shown in FIG. 6A, while the donor cornea 20′″ is depicted in FIG. 7A. The donor cornea 20′″ of FIG. 7A may be a cross-linked cornea of a cadaver or a tissue culture-grown cornea that has been cross-linked. Turning to FIG. 6B, it can be seen that an internal corneal pocket 28 is created in the cornea 16″″ of the host eye 10″″ (e.g., by using a suitable laser, which is indicated diagrammatically in FIG. 6B by lines 30).

In FIG. 7A, the cross-linking 18″ of the donor cornea 20′″ is diagrammatically illustrated. As mentioned in the preceding embodiments, it is to be understood that all or just a part of the donor cornea 20′″ may be cross-linked. Then, after the donor cornea 20′″ of FIG. 7A has been cross-linked (e.g., by using a photosensitizer in the form of riboflavin and UV radiation as described above), it can be seen that a cross-linked lamellar lenslet 26 is cut out from the remainder of the donor cornea 20′″ (e.g., by using a suitable laser, which is indicated diagrammatically in FIG. 7B by lines 32) such that it has the necessary shape for implantation into the host eye 10″″. As explained above, the cross-linked lamellar lenslet 26 may be cut from the donor cornea 20′″ and appropriately shaped using a femtosecond laser or an excimer laser. The cross-linked lamellar lenslet 26 is capable of being prepared to any requisite shape using either the femtosecond laser or the excimer laser. FIG. 7C illustrates the shaped cross-linked lamellar lenslet 26 after it has been removed from the remainder of the donor cornea 20′″.

Finally, as shown in FIG. 6C, the cross-linked lamellar lenslet 26 is implanted into the cornea 16″″ of the host eye 10″″ of the patient in the location where the pocket 28 was previously formed. Because the shape of the transplant corresponds to that of the pocket 28 formed in the eye 10″″, the transplant sits comfortably in its position in the host cornea 16″″. As described above, after implantation of the cross-linked lamellar lenslet 26 into the eye 10″″, the refractive errors of the eye 10″″ have been corrected because the cross-linked lamellar lenslet 26 has been appropriately shaped to compensate for the specific refractive errors of the host eye 10″″ prior to its implantation into the eye 10″″. In addition, as explained above, the implantation of the cross-linked lamellar lenslet 26 provides additional stability to an eye having keratoconus, keratoglobus, a thin cornea, or abnormal corneal curvature.

Another illustrative embodiment of a corneal lenslet implantation procedure with a cross-linked cornea is shown in FIGS. 8-14. In general, the procedure illustrated in these figures involves forming a two-dimensional cut into a cornea of an eye; creating a three-dimensional pocket in the cornea of the eye, cross-linking the interior stroma, and inserting a lenslet or lens implant into the three-dimensional pocket after the internal stromal tissue has been cross-linked.

Initially, in FIG. 8, the forming of a two-dimensional cut 115 into the cornea 112 of the eye 110 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 8, the two-dimensional cut 115 is formed by making an intrastromal incision in the cornea 112 of the eye 110 using a femtosecond laser (i.e., the incision is cut in the cornea 112 using the laser beam(s) 114 emitted from the femtosecond laser). Alternatively, the two-dimensional cut 115 may be formed in the cornea 112 of the eye 110 using a knife.

Then, in FIG. 9, the forming of a three-dimensional corneal pocket 116 in the cornea 112 of the eye 110 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 9, the three-dimensional corneal pocket 116 is formed by using a spatula 118. The formation of the intracorneal pocket 116 in the cornea 112 of the eye 110 allows one to gain access to the tissue surrounding the pocket 116 (i.e., the interior stromal tissue surrounding the pocket 116).

Turning again to FIGS. 8 and 9, in the illustrative embodiment, the corneal pocket 116 formed in the cornea 112 of the eye 110 may be in the form of an intrastromal corneal pocket cut into the corneal stroma. A femtosecond laser may be used to form a 2-dimensional cut into the cornea 112, which is then opened with a spatula 118 to create a 3-dimensional pocket 116. In one embodiment, a piece of the cornea 112 or a cornea which has a scar tissue is first cut with the femtosecond laser. Then, the cavity is cross-linked before filling it with an implant or inlay 128 to replace the lost tissue with a clear flexible inlay or implant 128 (see FIG. 12).

In one embodiment, a three-dimensional (3D) uniform circular, oval, or squared-shaped corneal pocket 116 is cut with a femtosecond laser and the tissue inside the pocket is removed to produce a three-dimensional (3D) pocket 116 to be cross-linked with riboflavin and implanted with a prepared implant.

After the pocket 116 is formed using the spatula 118, a photosensitizer is applied inside the three-dimensional pocket 116 so that the photosensitizer permeates the tissue surrounding the pocket 116 (see FIG. 10). The photosensitizer facilitates the cross-linking of the tissue surrounding the pocket 116. In the illustrative embodiment, the photosensitizer is injected with a needle 120 inside the stromal pocket 116 without lifting the anterior corneal stroma so as to cover the internal surface of the corneal pocket 116. In one or more embodiments, the photosensitizer or cross-linker that is injected through the needle 120 inside the stromal pocket comprises riboflavin, and/or a liquid suspension having nanoparticles of riboflavin disposed therein. Preferably, the cross-linker has between about 0.1% riboflavin to about 100% riboflavin therein (or between 0.1% and 100% riboflavin therein). Also, in one or more embodiments, an excess portion of the photosensitizer in the pocket 116 may be aspirated through the needle 120 until all, or substantially all, of the excess portion of the photosensitizer is removed from the pocket 116 (i.e., the excess cross-linker may be aspirated through the same needle so that the pocket 116 may be completely emptied or substantially emptied).

Next, turning to the illustrative embodiment of FIG. 11A, shortly after the photosensitizer is applied inside the pocket 116, the cornea 112 of the eye 110 is irradiated from the outside using ultraviolet (UV) radiation 122 so as to activate cross-linkers in the portion of the tissue surrounding the three-dimensional pocket 116, and thereby stiffen the cornea 112, prevent corneal ectasia of the cornea 112, and kill cells in the portion of the tissue surrounding the pocket 116. In the illustrative embodiment, the ultraviolet light used to irradiate the cornea 112 may have a wavelength between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). Also, in the illustrative embodiment, only a predetermined anterior stromal portion 124 of the cornea 112 to which the photosensitizer was applied is cross-linked (i.e., the surrounding wall of the corneal pocket 116), thereby leaving an anterior portion of the cornea 112 and a posterior stromal portion of the cornea 112 uncross-linked. That is, in the illustrative embodiment, the entire corneal area inside the cornea 112 exposed to the cross-linker is selectively cross-linked, thereby leaving the anterior part of the cornea 112 and the posterior part of the stroma uncross-linked. The portion of the cornea 112 without the cross-linker is not cross-linked when exposed to the UV radiation. In an alternative embodiment, the cornea 112 may be irradiated using wavelengths of light other than UV light as an alternative to, or in addition to being irradiated using the ultraviolet (UV) radiation 122 depicted in FIG. 11A. Also, microwave radiation may be used synergistically or additively to correct non-invasively the remaining refractive error(s) of the cornea.

Alternatively, as shown in FIG. 11B, a fiber optic 126 may be inserted into the corneal pocket 116 so as to apply the ultraviolet radiation and activate the photosensitizer in the wall of the corneal pocket 116. When the fiber optic 126 is used to irradiate the wall of the pocket 116, the ultraviolet radiation is applied internally, rather than externally as depicted in FIG. 11A.

Now, with reference to FIG. 12, it can be seen that, after the wall of the corneal pocket 116 has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, a lens implant 128 is inserted into the corneal pocket 116 in order to change the refractive properties of the eye. In particular, in the illustrated embodiment, the lens implant 128 is inserted through a small incision, and into the corneal pocket 116, using forceps or microforceps. In one or more embodiments, the lens implant 128 that is inserted inside the pocket 116 in the cornea 112 is flexible and porous. Also, in one or more embodiments, the lens implant 128 may comprise a hybrid lens implant with an organic outer portion and a synthetic inner portion. The organic outer portion of the hybrid lens implant may be made from a transparent, hydrophilic organic polymer, while the synthetic inner portion of the hybrid lens implant may be made from a transparent, gas permeable, porous flexible polymer. For example, the transparent, hydrophilic polymer forming the organic outer portion may be formed from collagen, chitosan, poloxamer, polyethylene glycol, or a combination thereof (or any other transparent hydrophilic coating which can be deposited over the entire lens surface), while the flexible polymer forming the synthetic inner portion of the hybrid lens implant may be formed from silicone, acrylic, polymethacrylate, hydrogel, or a combination thereof. The surface of the lens implant 128 may have the appropriate shape to reshape the cornea 112 or the dioptric power to nullify the remaining spheric or astigmatic error of the eye. More particularly, in one or more embodiments, the lens implant 128 may have one of: (i) a concave surface to correct myopic refractive errors (i.e., a minus lens for correcting nearsightedness), (ii) a convex surface to correct hyperopic refractive errors (i.e., a plus lens for correcting farsightedness), or (iii) a toric shape to correct astigmatic refractive errors.

In the illustrative embodiment, the irradiation of the cornea 112 using the ultraviolet (UV) radiation 122 only activates cross-linkers in the portion of the stromal tissue surrounding the three-dimensional pocket 116, and only kills the cells in the portion of the tissue surrounding the pocket 116, so as to leave only a thin layer of cross-linked collagen to prevent an immune response and rejection of the lens implant 128 and/or encapsulation by fibrocytes, while preventing post-operative dry eye formation. In addition to preventing encapsulation of the lens implant 128 by fibrocytes, the cross-linking of the stromal tissue surrounding the pocket 116 also advantageously prevents corneal haze formation around the lens implant 128. That is, the cross-linking of the stromal tissue surrounding the lens implant 128 prevents formation of myofibroblast from surrounding keratocytes, which then convert gradually to fibrocytes that appear as a haze, and then white encapsulation inside the cornea, thereby causing light scattering in front of the patient's eye.

As shown in FIGS. 13 and 14, the crosslinking procedure described above may be repeated after the lens implant 128 is implanted so as to prevent any cellular invasion in the area surrounding the implant 128. Initially, with reference to FIG. 13, the photosensitizer is reinjected inside the space between the lens implant 128 and the surrounding corneal tissue using a needle 120. In one or more embodiments, the needle 120 for injecting the photosensitizer may comprise a 30-32 gauge needle. Then, after the reinjection of the cross-linker, the cornea 112 is re-irradiated with ultraviolet radiation 122 to cross-link the tissue surrounding the lens implant 128 so as to prevent cellular migration towards the lens implant 128 (see FIG. 14).

In one or more embodiments, the lens implant or inlay 128 may be prepared ahead of time with known techniques, wherein the inlay 128 may be coated with a biocompatible material, such as collagen, elastin, polyethylene glycol, biotin, streptavidin, etc., or a combination thereof. The inlay 128 and the coating may be cross-linked with a photosensitizer or cross-linker, such as riboflavin, prior to being implanted into the pocket 116 in the cornea 112 of the eye.

In another embodiment, the lens implant or inlay 128 may be silicone, methacrylate, hydroxyethylmethacrylate (HEMA), or any other biocompatible transparent material, or a mixture thereof. The lens implant or inlay 128 also may be coated with materials, such as collagen or elastin, and may have a desired thickness of from 2 microns to 70 microns or more.

In yet another embodiment, the lens implant or inlay 128 is formed from an eye bank cornea, or a cross-linked eye bank cornea, etc. In general, there is a tremendous paucity of normal cadaver corneas for total or partial implants, such as for a corneal transplant of a corneal inlay. Because all the cellular elements are killed during the crosslinking of the corneal inlay, and because the corneal collagen is cross-linked and denatured, the remaining collagenous elements are not immunogenic when implanted inside the body or in the cornea of a patient. Advantageously, the prior cross-linking of the organic material, such as in the cadaver cornea, permits transplantation of the corneal inlay from an animal or human cornea or any species of animal to another animal or human for the first time without inciting a cellular or humoral response by the body, which rejects the inlay. Thus, cross-linking transparent cadaveric tissue for corneal transplantation, or as an inlay to modify of the refractive power of the eye, is highly beneficial to many patients who are on the waiting list for a corneal surgery. In addition, the surgery may be planned ahead of time without necessitating the urgency of the surgery when a fresh cadaver eye becomes available. In one or more embodiments, the collagens may be driven from the animal cornea, and cross-linked. Also, in one or more embodiments, the implant or inlay 128 may be made of cross-linked animal cornea or human cornea that is cut using a femtosecond laser to any desired shape and size, and then ablated with an excimer laser or cut with a femtosecond laser to a have a desired refractive power.

For example, as shown in FIG. 15, the lens implant or inlay 130 may be formed from an organic block of a polymer (e.g., donor cornea) by cutting the lens implant 130 using an excimer laser (e.g., by using the laser beam(s) 132 emitted from the excimer laser). Alternatively, referring to FIG. 16, the lens implant or inlay 130′ may be formed from an organic block 134 of a polymer (e.g., donor cornea) by cutting the lens implant 130′ from the block 134 using a femtosecond laser or a computerized femto-system (e.g., by using the laser beam(s) 136 emitted from the femtosecond laser).

In still another embodiment, as depicted in FIG. 17, the lens implant or inlay 130″ is made using three-dimensional (3D) printing technology or a molding technique in order to form the lens implant or inlay 130″ into the desired shape, size or thickness. The transparent material of the 3D-printed implant or inlay 130″ may be coated with one or more biocompatible polymers and cross-linked prior to the implantation.

In yet another embodiment, after the implantation of an intraocular lens, the remaining refractive error of the eye may be corrected by the implantation of a lens implant or inlay 128 in the cross-linked pocket 116 of the cornea 112, thereby eliminating the need for entering the eye cavity to replace the original intraocular lens.

In still another embodiment, the remaining refractive error of the eye is corrected after an intraocular lens implantation by placing an inlay 128 on the surface of the cornea 112 of the patient while the shape of the cornea 112 is corrected with an excimer laser and wavefront optimized technology so that the patient is provided instant input on its effect on his or her vision. In this embodiment, an inlay similar to a contact lens is placed on the cornea 112 that, after correction, matches the desired refractive correction of the eye, and then, subsequently, the inlay 128 is implanted inside the cross-linked corneal pocket 116.

In yet another embodiment, the implant or inlay 128 may be ablated with an excimer laser for implantation in the cross-linked pocket 116, or after cross-linking the exposed corneal stroma in LASIK surgery.

In still another embodiment, a small amount of hyaluronic acid or a viscous fluid is injected into the pocket 116 prior to the implantation of the implant or inlay 128 so as to simplify the insertion of the implant or inlay 128 in the corneal pocket 116.

In yet another embodiment, the implant or inlay 128 is prepared having four marking holes of 0.1-2 millimeter (mm) in diameter in the inlay periphery at an equally sized distances so that the implant 128 may be rotated with a hook, if desired, after the implantation as needed to match the axis of an astigmatic error of the eye during the surgery as measured simultaneously with a wavefront technology system, such as an Optiwave Refractive Analysis (ORA) system or Holos® system, which are commercially available for measurement of astigmatism or its axis.

In still another embodiment, the implant or inlay 128 is located on the visual axis and may provide 1 to 3 times magnification for patients whose macula is affected by a disease process needing magnifying glasses for reading, such as in age-related macular degeneration, macular edema, degenerative diseases of the retina, etc. Because these eyes cannot be used normally for reading without external magnifier glasses, providing magnification by a corneal implant to one eye assists the patients in being able to read with one eye and navigate the familiar environment with their other eye.

In yet another embodiment, a part of the corneal stroma is removed from the eye of the patient, and its surface is corrected with an excimer laser to a desired refraction. Then, the removed part of the corneal stroma is cross-linked, and implanted back into the corneal pocket so as to correct the refractive power of the cornea.

In still another embodiment, the surface of the cornea 112 is treated after surgery in all cases daily with an anti-inflammatory agent, such as steroids, nonsteroidal anti-inflammatory drugs (NSAIDs), immune-suppressants, such as cyclosporine A or mycophenolic acid, anti-proliferative agents, antimetabolite agents, or anti-inflammatory agents (e.g., steroids, NSAIDS, or antibiotics etc.) to prevent inflammatory processes after the corneal surgery, inlay implantation or crosslinking, while stabilizing the integrity of the implant 128 and preventing future cell growth in the organic implant or the adjacent acellular corneal tissue. In this embodiment, the medication is injected in the corneal pocket 116 along with the implantation or the implant 128 is dipped in the medication first, and then implanted in the cross-linked corneal pocket 116.

In yet another embodiment, a cross-linked corneal inlay is placed over the cross-linked corneal stroma after a LASIK incision, and is abated to the desired size with an excimer laser using a topography guided ablation. By means of this procedure, the refractive power of the eye is corrected, while simultaneously providing stability to an eye prone to conceal ectasia postoperatively after a LASIK surgery. Then, the LASIK flap is placed back over the implant.

Yet another illustrative embodiment of a corneal lenslet implantation procedure with a cross-linked cornea is shown in FIGS. 18-23. In general, the procedure illustrated in these figures involves initially making an intrastromal square pocket surrounding the visual axis of the eye, and then, after forming the initial square pocket, a three-dimensional circular portion of diseased or weak stromal tissue is cut, removed, and replaced with a circular implant which fits into the circle that borders the four sides of the square. A front view of the cornea 212 of the eye 210 with the centrally-located visual axis 214 is illustrated in FIG. 18. Advantageously, in the illustrative embodiment of FIGS. 18-23, corneal tissue removal around the visual axis is greatly facilitated, and nearly perfect centration of the lens implant or inlay 220 about the visual axis is possible because the lens implant 220 fits within a depressed circular recess at the bottom of the pocket 216. As such, the undesirable decentering of the lens implant is prevented.

Initially, in FIG. 19, the forming of an intrastromal square-shaped pocket 216 surrounding the visual axis 214 (represented by a plus sign) in the cornea 212 of the eye 210 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 19, the square-shaped pocket 216 is formed by making a two-dimensional intrastromal incision in the cornea 212 of the eye 210 using a femtosecond laser (i.e., the incision is cut in the cornea 212 using the laser beam(s) emitted from the femtosecond laser).

Then, in FIG. 20, the removal of a three-dimensional circular portion 218 of diseased or weak stromal tissue in the cornea 212 of the eye 210 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 20, the three-dimensional circular stromal tissue portion 218 has a first diameter, which is less than a width of the square-shaped pocket 216 so that the three-dimensional circular stromal tissue portion 218 is disposed within the boundaries of the square-shaped pocket 216. The three-dimensional circular stromal tissue portion 218′ depicted in FIG. 21 is generally similar to that illustrated in FIG. 20, except that the three-dimensional circular stromal tissue portion 218′ depicted in FIG. 21 has a second diameter that is slightly larger than the first diameter of the three-dimensional circular stromal tissue portion 218 in FIG. 20. As such, the periphery of the three-dimensional circular stromal tissue portion 218′ depicted in FIG. 21 is disposed closer to the square-shaped pocket 216, but still within the confines of the square-shaped pocket 216. In the illustrative embodiment, the three-dimensional circular stromal tissue portion 218, 218′ may be removed using forceps or micro-forceps. In an exemplary embodiment, the diameter of the circular stromal tissue portion 218, 218′ that is removed from the cornea 212 is between approximately 5 millimeters and approximately 8 millimeters, inclusive (or between 5 millimeters and 8 millimeters, inclusive).

In an alternative embodiment of the corneal lenslet implantation procedure, three (3) sequential cuts may be made in the stromal portion of the cornea 212 of the eye 210 using a femtosecond laser in order to form the pocket. First, a lower circular cut or incision centered about the visual axis (i.e., a lower incision with the patient in a supine position) is made using the femtosecond laser. Then, a second vertical cut is made above the lower incision using the femtosecond laser to form the side(s) of a circular cutout portion. Finally, a third square or circular cut (i.e., an upper incision) is made above the vertical cut using the femtosecond laser. In the illustrative embodiment, the lower incision is parallel to the upper incision, and the vertical cut extends between lower incision and the upper incision. In this alternative embodiment, the three-dimensional circular stromal tissue cutout portion bounded by the lower incision on the bottom thereof, the vertical cut on the side(s) thereof, and the upper incision on the top thereof is removed from the cornea 212 of the eye 210 using a pair of forceps. A cavity formed by the upper incision facilitates the removal of the three-dimensional circular stromal tissue cutout portion. As described above, the third cut or incision formed using the femtosecond laser may be an upper circular cut that is larger than the lower circular cut, rather than an upper square cut that is larger than the lower circular cut.

Turning to FIG. 22, after the three-dimensional circular stromal tissue portion 218, 218′ is removed, a photosensitizer is applied inside the pocket 216 so that the photosensitizer permeates the tissue surrounding the pocket 216. The photosensitizer facilitates the cross-linking of the tissue surrounding the pocket 216. In the illustrative embodiment, the photosensitizer is injected with a needle 222 inside the stromal pocket 216. In one or more embodiments, the photosensitizer or cross-linker that is injected through the needle 222 inside the stromal pocket 216 comprises riboflavin, and/or a liquid suspension having nanoparticles of riboflavin disposed therein. Preferably, the cross-linker has between about 0.1% riboflavin to about 100% riboflavin therein (or between 0.1% and 100% riboflavin therein). Also, in one or more embodiments, an excess portion of the photosensitizer in the pocket 216 may be aspirated through the needle 222 until all, or substantially all, of the excess portion of the photosensitizer is removed from the pocket 216 (i.e., the excess cross-linker may be aspirated through the same needle 222 so that the pocket 216 may be completely emptied or substantially emptied).

Next, turning again to the illustrative embodiment of FIG. 22, shortly after the photosensitizer is applied inside the pocket 216, the cornea 212 of the eye 210 is irradiated from the outside using ultraviolet (UV) radiation 224 so as to activate cross-linkers in the portion of the tissue surrounding the three-dimensional pocket 216, and thereby stiffen the cornea 212, prevent corneal ectasia of the cornea 212, and kill cells in the portion of the tissue surrounding the pocket 216. In the illustrative embodiment, the ultraviolet light used to irradiate the cornea 212 may have a wavelength between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). Also, in the illustrative embodiment, only a predetermined anterior stromal portion of the cornea 212 to which the photosensitizer was applied is cross-linked (i.e., the surrounding wall of the corneal pocket 216), thereby leaving an anterior portion of the cornea 212 and a posterior stromal portion of the cornea 212 uncross-linked. That is, in the illustrative embodiment, the entire corneal area inside the cornea 212 exposed to the cross-linker is selectively cross-linked, thereby leaving the anterior part of the cornea 212 and the posterior part of the stroma uncross-linked. The portion of the cornea 212 without the cross-linker is not cross-linked when exposed to the UV radiation. In an alternative embodiment, the cornea 212 may be irradiated using wavelengths of light other than UV light as an alternative to, or in addition to being irradiated using the ultraviolet (UV) radiation 224 depicted in FIG. 22. Also, microwave radiation may be used synergistically or additively to correct non-invasively the remaining refractive error(s) of the cornea. In addition, in an alternative embodiment, the ultraviolet (UV) radiation may be applied after the implantation of the lens implant 220 to perform the crosslinking, rather than before the implantation of the lens implant 220 as described above. Further, rather than applying the ultraviolet (UV) radiation from outside the cornea 212, the stromal tissue of the pocket 216 may be irradiated from inside by means of a fiber optic, before or after the implantation of the lens implant 220.

Now, with combined reference to FIGS. 22 and 23, it can be seen that, before or after the wall of the corneal pocket 216 has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, a circular lens implant 220 is inserted into the circular recess at the bottom of the pocket 216 formed by the three-dimensional circular stromal tissue cutout portion 218, 218′ that was removed. That is, the circular lens implant 220 fits within the periphery of the circular recess that borders the four sides of the squared-shaped pocket 216. In particular, in the illustrated embodiment, the circular lens implant 220 is inserted through a small incision, and into the circular recess at the bottom of the pocket 216 using forceps or microforceps. In the illustrative embodiment, the flexible lens implant 220 may be folded, inserted through the small incision, placed inside the circular recess at the bottom of the pocket 216, and finally unfolded through then small incision. In one or more embodiments, the lens implant 220 that is inserted inside the pocket 216 in the cornea 212 is flexible and porous. Also, in one or more embodiments, the lens implant 220 may comprise a hybrid lens implant with an organic outer portion and a synthetic inner portion. The organic outer portion of the hybrid lens implant may be made from a transparent, hydrophilic organic polymer, while the synthetic inner portion of the hybrid lens implant may be made from a transparent, gas permeable, porous flexible polymer. For example, the transparent, hydrophilic polymer forming the organic outer portion may be formed from collagen, chitosan, poloxamer, polyethylene glycol, or a combination thereof (or any other transparent hydrophilic coating which can be deposited over the entire lens surface), while the flexible polymer forming the synthetic inner portion of the hybrid lens implant may be formed from silicone, acrylic, polymethacrylate, hydrogel, or a combination thereof.

Advantageously, the lens implant 220 of the aforedescribed illustrative embodiment always remains perfectly centered around the visual axis 214 of the eye 210, and will not move because it is disposed within the circular recess at the bottom of the pocket 216. As explained above, the lens implant 220 may be formed from an organic material, synthetic material, polymeric material, and combinations thereof. The lens implant 220 may replace either a diseased tissue or create a new refractive power for the eye 210, as explained hereinafter.

In the illustrative embodiment, the lens implant 220 may correct the refractive errors of the eye 210. The refractive error correction may be done by the lens implant 220 having a curvature that changes the corneal surface of the cornea 212. Alternatively, the lens implant 220 may have a different index of refraction that corrects the refractive power of the cornea 212. In the illustrative embodiment, the lens implant 220 may have the appropriate shape to reshape the cornea 212 or the dioptric power to nullify the remaining spheric or astigmatic error of the eye. More particularly, in one or more embodiments, the lens implant 220 may have one of: (i) a concave anterior surface to correct myopic refractive errors (i.e., a minus lens for correcting nearsightedness), (ii) a convex anterior surface to correct hyperopic refractive errors (i.e., a plus lens for correcting farsightedness), or (iii) a toric shape to correct astigmatic refractive errors.

In the illustrative embodiment, the irradiation of the cornea 212 using the ultraviolet (UV) radiation 224 only activates cross-linkers in the portion of the stromal tissue surrounding the three-dimensional pocket 216, and only kills the cells in the portion of the tissue surrounding the pocket 216, so as to leave only a thin layer of cross-linked collagen to prevent an immune response and rejection of the lens implant 220 and/or encapsulation by fibrocytes, while preventing post-operative dry eye formation. In addition to preventing encapsulation of the lens implant 220 by fibrocytes, the cross-linking of the stromal tissue surrounding the pocket 216 also advantageously prevents corneal haze formation around the lens implant 220. That is, the cross-linking of the stromal tissue surrounding the lens implant 220 prevents formation of myofibroblast from surrounding keratocytes, which then convert gradually to fibrocytes that appear as a haze, and then white encapsulation inside the cornea, thereby causing light scattering in front of the patient's eye.

It is readily apparent that the aforedescribed corneal transplant procedures offer numerous advantages. First, the implementation of the aforedescribed corneal transplant procedures reduces the likelihood that the implanted cornea will be rejected by the patient. Secondly, the aforedescribed corneal transplant procedures enable the clarity of the transplanted cornea to be preserved. Finally, the aforedescribed corneal transplant procedures reduce the likelihood that the transplanted cornea will be invaded by migrating cells, such as migrating cells that might initiate an immune response such as macrophage, lymphocytes or leucocytes or vascular endothelial cells. These types of migrating cells are discouraged by the cross-linked corneal collagen which does not provide an easily accessible tissue to invade. In addition, the use of above described tissue adhesives reduces the surgical procedure significantly. Moreover, the aforedescribed corneal lenslet implantation procedures modify the cornea so as to better correct ametropic conditions. Furthermore, the corneal lenslet implantation procedures described above prevent the lens implant from moving around inside the cornea once implanted, thereby ensuring that the lens implant remains centered about the visual axis of the eye.

With reference to the illustrative embodiment of FIGS. 24-29, an exemplary method of preventing capsular opacification and fibrosis utilizing an accommodative intraocular lens implant will be explained. In general, the procedure illustrated in FIGS. 24-29 involves treating patients in need of cataract surgery and a replacement intraocular lens.

Initially, referring to FIG. 24, it can be seen that the eye 300 undergoing cataract surgery generally includes a cornea 302, an anterior chamber 304, an iris 306, a lens capsule or capsular bag 308, ciliary body 309, lens zonules 310, a vitreous cavity 314, a sclera 316, and an optic nerve 318. As shown in FIG. 24, the eye 300 has a cataract 312 (i.e., a cloudy lens), thereby requiring that cataract surgery be performed on the eye 300 of the patient.

In FIG. 25, the first stage of the removal of the cortex and nucleus of the natural lens of the eye 300 containing the cataract 312 is diagrammatically illustrated. Specifically, in FIG. 25, the cloudy natural lens of the eye 300 is shown being broken apart into lens fragments by utilizing a femtosecond laser (i.e., the natural lens is broken apart by using the laser beam(s) 320 emitted from the femtosecond laser). The natural lens is initially broken apart into fragments so that it is capable of being more easily removed from the lens capsule 308 of the eye 300.

Then, referring to FIG. 26, the second stage of the removal of the cortex and nucleus of the natural lens of the eye 300 containing the cataract 312 is diagrammatically shown. In particular, as depicted in FIG. 26, the lens fragments of the natural lens are being removed from the lens capsule 308 of the eye 300 using an ultrasonic probe 322. More particularly, the ultrasonic probe 322 irrigates and aspirates the lens fragments of the natural lens. In addition, the ultrasonic probe 322 may also be used to aspirate a substantial portion of the lens epithelium from the lens capsule 308 through an additional hole made in the lens capsule 308 and used as a bimanual system. That is, in the illustrative embodiment, the ultrasonic probe 322 may be used to aspirate as much of the lens epithelium as possible from the lens capsule 308 to prevent the undesirable propagation of lens epithelium cells following the cataract surgery.

Next, in FIG. 27, the injection of a cross-linker or photosensitizer (e.g., riboflavin) into the capsular bag 308 of the eye 300 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 27, the cataract 312 has been removed from the capsular bag 308, which leaves the vast majority of the capsular bag 308 intact. Then, as shown in FIG. 27, a photosensitizer is applied inside the capsular bag 308 so that the photosensitizer permeates the tissue in both the anterior and posterior portions of the capsular bag 308. The photosensitizer facilitates the cross-linking of the tissue in the anterior and posterior portions of the capsular bag 308. In the illustrated embodiment of FIG. 27, the photosensitizer is injected with a needle 324 into the capsular bag 308 of the eye 300 by inserting the needle 324 through the anterior chamber 304 of the eye 300, and into the capsular bag 308 through the anterior wall of the capsular bag 308. In one or more embodiments, the photosensitizer or cross-linker that is injected through the needle 324 into the capsular bag 308 comprises riboflavin, and/or a biocompatible fluid having nanoparticles of riboflavin disposed therein. Preferably, the cross-linker has between about 0.1% riboflavin to about 100% riboflavin therein (or between 0.1% and 100% riboflavin therein). Also, in one or more embodiments, an excess portion of the photosensitizer in the capsular bag 308 may be aspirated through the needle 324 until all, or substantially all, of the excess portion of the photosensitizer is removed from the capsular bag 308 (i.e., the excess cross-linker may be aspirated through the same needle 324 so that the capsular bag 308 may be completely emptied or substantially emptied). Also, in one or more embodiments, in order to kill the remaining lens epithelial cells that are generally attached to the rear side of the anterior portion of the lens capsule 308, the riboflavin may be in a relatively hypotonic solution that permits the lens cells to swell and makes them easier to remove or kill during the irradiation step described hereinafter.

Next, turning to FIG. 28, shortly after the photosensitizer is applied inside the capsular bag 308, the entire capsular bag 308 of the eye 300 (i.e., both the anterior portion and posterior portion of the lens capsule 308) is irradiated using a fiber optic 326 delivering ultraviolet (UV) radiation 328 so as to damage the remaining lens epithelial cells with UV laser light, thereby preventing capsular opacification and fibrosis. In the illustrative embodiment, the irradiation of the lens capsule 308 includes the anterior portion of the lens capsule 308 in order to prevent growth of the damaged lens epithelial cells and prevent cell migration and opacification because, in some cases, epithelial cells are still left in the lens capsule 308 after irrigation and aspiration of the lens fragments. Advantageously, the killing of the epithelial cells by irradiation prevents the further growth of the lens epithelial cells, and prevents their migration toward the posterior portion of the lens capsule 308 where they later become opaque. Also, in the illustrative embodiment, a painting technique may be utilized to deliver the ultraviolet light 328 to the capsular bag 308 of the eye 300 (i.e., the fiber optic 326 may be manipulated in such a manner by the surgeon so as to “paint” the ultraviolet light 328 on the capsular bag 308). Also, in the illustrative embodiment, ultraviolet (UV) radiation 328 may have a wavelength between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). In an alternative embodiment, the capsular bag 308 of the eye 300 may be irradiated using another wavelength of light as an alternative to, or in addition to being irradiated using ultraviolet (UV) radiation.

In an alternative embodiment, the anterior portion of the capsular bag 308 may be irradiated from outside the capsular bag 308 rather than from inside the capsular bag 308 as depicted in FIG. 28. In this embodiment, the fiber optic 326 may be disposed in the anterior chamber 304 of the eye 300 so that the ultraviolet (UV) light may be directed towards the anterior portion of the capsular bag 308. For example, the fiber optic 326 may be disposed at an acute angle relative to the capsular bag 308, but not perpendicular to the capsular bag 308 (so that the macula is protected and not damaged by the UV light emitted from the fiber optic 326).

Finally, referring to FIG. 29, it can be seen that, after the tissue of the capsular bag 308 has been irradiated, a transparent polymer 332 is injected into the capsular bag 308 of the eye 300 using a needle 330 in order to form an accommodative intraocular lens implant for replacing the cortex and nucleus of the cloudy natural lens that was removed from the eye 300. In particular, in the illustrative embodiment, the needle 330 for injecting the transparent polymer 332 forming the accommodative intraocular lens is inserted into the capsular bag 308 of the eye 300 through an anterior hole or holes in the lens capsule 308. The hole or holes in the anterior chamber are plugged after the transparent polymer forming the accommodative intraocular lens hardens. In the illustrative embodiment, the transparent polymer that forms the accommodative intraocular lens remains flexible after the transparent polymer hardens or solidifies. Also, in the illustrative embodiment, after the transparent polymer that forms the accommodative intraocular lens is injected into the capsular bag 308 of the eye using the needle 330, the refractive power of the accommodative intraocular lens is adjusted using a wavefront technology unit intraoperatively so that the intraocular lens is able to be focused for a far distance without accommodation, and additionally is able to be focused for a near distance during accommodation by increasing the refractive power of the intraocular lens using the natural accommodative mechanism of the eye 300. Advantageously, intraoperative units utilizing wavefront technology are capable of indicating perfect refraction. During the injection process, both overfilling or under filling of the capsular bag 308 is not desirable because it does not provide proper refractive power for the lens and the eye 300.

In a further embodiment, the transparent polymer 332 that forms the accommodative intraocular lens implant is partially polymerized when injected into the capsular bag 308, and the transparent polymer becomes completely polymerized within a predetermined time period (e.g., within 5 to 20 minutes) after being injected into the capsular bag 308. In general, the polymerization time of the accommodative intraocular lens implant depends on the polymerization initiator that is used.

In one or more further embodiments, cataract surgery and glaucoma surgery with or without stent implantation may be done in a single session, wherein the photosensitizer is initially injected in the lens capsule after removal of the lens cortex and the nucleus. Then, a fiber optic is used to apply ultraviolet (UV) radiation so as to damage the lens epithelial cells and prevent their cellular proliferation. Immediately thereafter, the tissue around the surgical opening made in the eye wall during the glaucoma surgery with or without the shunt placement to drain the aqueous fluid outside the eye, is stained with the photosensitizer that was injected in the lens capsule. The photosensitizer migrates outside the eye through the surgical hole in the eye wall. The tissue, which is bathed by the photosensitizer (e.g., riboflavin), is then cross-linked with UV radiation applied through a fiber optic from the inside the eye or outside through the conjunctiva over the surgical hole or the shunt, regardless of the presence of a stent. The procedure achieves two goals simultaneously by preventing lens epithelial proliferation in the lens capsule, and by preventing fibroblast proliferation around the surgical hole of the tube.

Now, referring to the illustrative embodiment of FIGS. 30-41, an exemplary method for prevention of capsular opacification and fibrosis after cataract extraction, and for the prevention of fibrosis around a shunt or stent after glaucoma surgery will be explained. In general, the procedure illustrated in FIGS. 30-41 involves treating patients in need of both cataract surgery and glaucoma surgery. In the illustrative embodiment of FIGS. 30-41, the cataract and glaucoma surgeries are performed sequentially. However, as described hereinafter, the cataract and glaucoma surgeries may also be performed as two separate procedures. In these embodiments, the intraocular pressure (IOP) measurement is independent for a patient in need of cataract surgery and/or a glaucoma surgery.

Initially, referring to FIG. 30, it can be seen that the eye 400 undergoing cataract surgery generally includes a cornea 402, an anterior chamber 404, an iris 406, a lens capsule or capsular bag 408, lens zonules 410, a vitreous cavity 414, and a conjunctiva 416. As shown in FIG. 30, the eye 400 has a cataract 412 (i.e., a cloudy lens), thereby requiring that cataract surgery be performed on the eye 400 of the patient.

In FIG. 31, the injection of a photosensitizer (e.g., riboflavin) into the posterior portion of the capsular bag 408 of the eye 400 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 31, the cataract 412 has been removed from the capsular bag 408, which leaves the posterior portion of the capsular bag 408 intact. Then, as shown in FIG. 31, a photosensitizer is applied inside the capsular bag 408 so that the photosensitizer permeates the tissue in the posterior portion of the capsular bag 408. The photosensitizer facilitates the cross-linking of the tissue in the posterior portion of the capsular bag 408. In the illustrated embodiment of FIG. 31, the photosensitizer is injected with a needle 418 into the capsular bag 408 of the eye 400 by inserting the needle 418 through the anterior chamber 404 of the eye 400, and into the capsular bag 408. In one or more embodiments, the photosensitizer or cross-linker that is injected through the needle 418 into the capsular bag 408 comprises riboflavin, and/or a biocompatible fluid having nanoparticles of riboflavin disposed therein. Preferably, the cross-linker has between about 0.1% riboflavin to about 100% riboflavin therein (or between 0.1% and 100% riboflavin therein). Also, in one or more embodiments, an excess portion of the photosensitizer in the capsular bag 408 may be aspirated through the needle 418 until all, or substantially all, of the excess portion of the photosensitizer is removed from the capsular bag 408 (i.e., the excess cross-linker may be aspirated through the same needle 418 so that the capsular bag 408 may be completely emptied or substantially emptied).

Next, turning to FIG. 32, shortly after the photosensitizer is applied inside the capsular bag 408, the remaining posterior portion of the capsular bag 408 of the eye 400 is irradiated using a fiber optic 420 delivering ultraviolet (UV) radiation 422 so as to damage the remaining lens epithelial cells with UV laser light, thereby preventing capsular opacification and fibrosis. In the illustrative embodiment, a painting technique may be utilized to deliver the ultraviolet light 422 to the posterior portion of the capsular bag 408 of the eye 400 (i.e., the fiber optic 420 may be manipulated in such a manner by the surgeon so as to “paint” the ultraviolet light 422 on the posterior portion of the capsular bag 408). Also, in the illustrative embodiment, ultraviolet (UV) radiation 422 may have a wavelength between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). In an alternative embodiment, the posterior portion of the capsular bag 408 of the eye 400 may be irradiated using another wavelength of light as an alternative to, or in addition to being irradiated using ultraviolet (UV) radiation.

Now, with reference to FIG. 33, it can be seen that, after the cataract 412 has been removed and the posterior portion of the capsular bag 408 has been irradiated, an intraocular lens 424 is implanted into the capsular bag 408 of the eye 400 in order to replace the cloudy natural lens that was removed. In particular, in the illustrative embodiment, the intraocular lens 424 is inserted into the capsular bag 408 of the eye 400 through the anterior opening 426 in the lens capsule 408.

Next, turning to FIGS. 34-38, the stent implantation and fibrosis prevention steps of the combined cataract extraction and glaucoma surgical procedure will be explained. Initially, the eye 400 with the implanted intraocular lens 424 therein is shown in FIG. 34.

In FIG. 35, the insertion of a glaucoma stent 430 through the anterior chamber 404, and into the subconjunctival space 432 of the eye 400 is diagrammatically illustrated. In particular, in the illustrated embodiment, the glaucoma stent 430 may be inserted into the subconjunctival space 432 of the eye 400 using a pair of forceps or microforceps 428. A detail view of the insertion of the glaucoma stent 430 is shown in FIG. 36. Once inserted, the glaucoma stent 430 extends from the anterior chamber 404 to the subconjunctival space 432.

Then, as shown in FIG. 37, the injection of a photosensitizer (e.g., riboflavin) into the anterior chamber 404 so that the photosensitizer diffuses into the tissue surrounding the glaucoma stent 430 is diagrammatically illustrated. In particular, as shown in the illustrative embodiment of FIG. 37, a photosensitizer is applied inside the anterior chamber 404 of the eye 400 and then a diffused stream 436 of the photo sensitizer travels through the central opening of the glaucoma stent 430, and into the subconjunctival space 432 so that the photosensitizer permeates the tissue surrounding the glaucoma stent 430. The photosensitizer facilitates the cross-linking of the tissue surrounding the glaucoma stent 430. In the illustrated embodiment of FIG. 37, the photosensitizer is injected with a needle 434 into the anterior chamber 404 of the eye 400 by inserting the needle 434 into the anterior chamber 404 of the eye 400, and letting the photosensitizer diffuse through the central opening in the glaucoma stent 430. In one or more embodiments, the photosensitizer or cross-linker that is injected through the needle 434 into the anterior chamber 404 comprises riboflavin, and/or a biocompatible fluid having nanoparticles of riboflavin disposed therein. Preferably, the cross-linker has between about 0.1% riboflavin to about 100% riboflavin therein (or between 0.1% and 100% riboflavin therein).

Next, turning to FIG. 38, shortly after the photosensitizer is applied inside the anterior chamber 404, the subconjunctival space 432 of the eye 400 is irradiated using a fiber optic 438 carrying ultraviolet (UV) light so as to cross-link the tissue surrounding the glaucoma stent 430, thereby preventing fibrosis around the stent 430 outflow. In the illustrative embodiment, a painting technique may be utilized to deliver the ultraviolet light to the subconjunctival space 432 of the eye 400 (i.e., the fiber optic 438 may be manipulated in such a manner by the surgeon so as to “paint” the subconjunctival space 432 with the ultraviolet light). Also, in the illustrative embodiment, ultraviolet (UV) radiation may have a wavelength between about 370 nanometers and about 380 nanometers (or between 370 nanometers and 380 nanometers). In an alternative embodiment, the subconjunctival space 432 of the eye 400 may be irradiated using another wavelength of light as an alternative to, or in addition to being irradiated using ultraviolet (UV) radiation.

An alternative embodiment of the invention is depicted in FIG. 39. In particular, glaucoma drainage surgery is illustrated in FIG. 39. As shown in FIG. 39, the eye 400 undergoing glaucoma drainage surgery generally includes a cornea 402, an anterior chamber 404, an iris 406, a lens capsule or capsular bag 408 with an intraocular lens 424 disposed therein, a vitreous cavity 414, a conjunctiva 416, an optic nerve 442, and a sclera 444. Similar to the application of the photosensitizer described above with regard to FIG. 37, in the FIG. 39 embodiment, the photosensitizer (e.g., riboflavin in a biocompatible fluid) is injected into the anterior chamber 404 of the eye 400 using a needle 434. Then, a diffused stream 436 of the photosensitizer injected from the needle 434 travels through the opening or shunt 440 in the eye wall, and into the subconjunctival space 432 so that the photosensitizer permeates the tissue surrounding the opening or shunt 440. After which, with reference again to FIG. 39, the subconjunctival space 432 of the eye 400 is irradiated using a fiber optic 438 carrying ultraviolet (UV) light so as to cross-link the tissue surrounding the opening or shunt 440, thereby preventing fibrosis around the opening or shunt 440 outflow. A detail view of the application of the photosensitizer to the opening or shunt 440 is shown in FIG. 40. The opening or shunt 440 illustrated in FIGS. 39 and 40 is located in the angle of the eye between the iris 406 and the cornea 402. The opening or shunt 440 connects the anterior chamber 404 of the eye 400 to the subconjunctival space 432.

Another alternative embodiment of the invention is depicted in FIG. 41. In particular, a stent 446 positioned in the suprachoroidal space 447 of the eye 400 is illustrated in FIG. 41. More particularly, the glaucoma stent 446 in FIG. 41 extends from the angle of the anterior chamber 404 of the eye 400 to the suprachoroidal space 447. As shown in FIG. 41, the eye 400 undergoing glaucoma surgery generally includes a cornea 402, an anterior chamber 404, an iris 406, a lens capsule or capsular bag 408 with an intraocular lens 424 disposed therein, a vitreous cavity 414, an optic nerve 442, a sclera 444, a retina 448, and a choroid 450. Similar to the application of the photosensitizer described above with regard to FIG. 39, in the FIG. 41 embodiment, the photosensitizer (e.g., riboflavin in a biocompatible fluid) is injected into the anterior chamber 404 of the eye 400 using a needle 434. Then, a diffused stream 436 of the photosensitizer injected from the needle 434 travels through the glaucoma stent 446 in the suprachoroidal space 447 of the eye 400, and into the suprachoroidal space 447 so that the photosensitizer permeates the tissue surrounding the glaucoma stent 446. After which, with reference again to FIG. 41, the suprachoroidal space 447 of the eye 400 is irradiated using a fiber optic 438 carrying ultraviolet (UV) laser light so as to cross-link the tissue surrounding the glaucoma stent 446, thereby preventing fibrosis around the glaucoma stent 446 outflow.

In another embodiment, the application of the photosensitizer and the irradiation of the tissue surrounding the glaucoma stent 446 is repeated one or more additional times to cross-link the tissue surrounding the stent 446 again so as to prevent any cellular invasion in the area surrounding the stent 446.

In still another embodiment, the cataract surgery and the glaucoma surgery with or without stent implantation is done in two sessions. Initially, the photosensitizer is used to kill the lens epithelial cells using a fiber optic applying ultraviolet (UV) radiation, while in a subsequent glaucoma surgery with or without a stent, a photosensitizer (e.g., riboflavin) is injected in the anterior chamber after the glaucoma surgery with or without a stent and the wall of the outflow hole and the tissue in the subconjunctival space is then irradiated with ultraviolet (UV) light from the external side with a fiber optic in a painting fashion with the desired power to cross-link the collagenous tissue around the eye wall opening or around the stent to kill the cells, thereby preventing the cells from migrating in the surgical area and closing the outflow channel.

In yet another embodiment, in a previous glaucoma surgery involving a shunt or drainage tube, a minimal amount (e.g., 0.02 to 0.1 milliliters or less) of the photosensitizer (e.g., riboflavin) is injected in the anterior chamber of the eye so as to diffuse out of the surgically created hole or a shunt. Then, immediately thereafter, ultraviolet (UV) radiation is applied in an oscillatory painting fashion over the end of the drainage tube or stent, or over the surgically produced opening, at the desired power and duration in order to cross-link the tissue that comes into contact with the photosensitizer, etc.

In still another embodiment, the radiation is done shortly after injection of the photosensitizer (e.g., 5 to 60 seconds thereafter) or slightly longer after injection of the photosensitizer to prevent crosslinking or damage to the conjunctival superficial vessels or the conjunctival epithelial surface, so as to only crosslink the deeper laying tissue of the subtenon space or choroidal tissue immediately in contact with the photosensitizer over the pars plana. This process may be repeated to stabilize the tissue and further prevent tissue adhesion and encapsulation of the drainage shunt.

In one embodiment, the implant has a collagenous coating. The device may be in the form of a stent or a glaucoma drainage device connecting the fluid produced inside the eye to outside, either in the choroid or under the conjunctiva. The collagen coating can be conjugated with a photosensitizer that can be cross-linked after implantation with ultraviolet (UV) radiation or another wavelength of light that is applied to cross-link the collagen surrounding the implant, and to prevent cell growth or migration over the implant and encapsulation of the implant. Advantageously, by preventing cell growth or migration over the implant and the encapsulation of the implant, the aqueous fluid has unimpeded access to the subconjunctival space or the choroidal space.

In another embodiment, a collagen conjugated with a photosensitizer is injected surrounding the body of the implant after the stent or shunt implantation, and then the polymeric collagen and the surrounding tissue is cross-linked so as to provide an area for diffusion of fluid, and to kill the surrounding cells and prevent encapsulation of the implant or a part of it.

In yet another embodiment, the photosensitizer may be injected in the lens capsule after removal of the lens nucleus and the lens cortex so as to cross-link the remaining lens epithelial cells with ultraviolet (UV) light applied through a fiber optic in a painting fashion with an appropriate power to damage the epithelial cells prior to implantation of an intraocular lens (IOL), thereby preventing encapsulation and cell proliferation of the remaining epithelial lens cells in the lens capsule that create a fibrous-like encapsulation closing the space between the anterior and posterior leaflet of the remaining lens capsule or around an implanted intraocular lens. This cell proliferation causes a significant posterior capsular opacification about 3 to 12 months after cataract surgery in over 80% of the patients, or the implant may be tilted as a result of force applied to it, thus requiring laser surgery to cut the capsule open for the patient to have a clear view to the outside for uninterrupted light to reach the retina.

Now, referring to FIGS. 42-46, another embodiment of a glaucoma stent 520 and a surgical procedure using the stent 520 will be described. Initially, referring to the perspective view of the stent 520 in FIG. 42, it can be seen that the glaucoma stent 520 comprises a flexible tube with an external coating 522 disposed on the outside of the stent 520 and an internal coating 524 disposed on the inside of the stent 520. The external and internal stent coating 522, 524 is very important for the surgical procedure. Unless the external and internal stent coating 522, 524 is done with a substance, such as collagen, elastin, and/or polyethylene glycol (PEG), the stent 520 can irritate the surrounding tissue and excite cell migration and encapsulation. The coating may be applied to the stent 520 before or after the implantation of the stent 520. Preferably, the glaucoma stent 520 is formed from a solid, flexible, or semi-flexible material. For example, the stent material may be silicone-based or a mixture of polymers (e.g. acrylic and Hydroxyethyl methacrylate (HEMA), or HEMA alone, etc.) that preferably create a soft stent 520 for its placement under the conjunctiva of the eye. However, the stent 520 may also be implanted under the sclera of the eye. The glaucoma stent 520 may have a diameter between approximately 50 microns and approximately 700 microns (or between 50 microns and 700 microns), and the stent 520 may have a length between approximately 5 millimeters (mm) and approximately 15 millimeters (or between 5 millimeters and 15 millimeters). The diameter and the length of the stent 520 ultimately determine how much fluid is drained at a certain, desired intraocular pressure. This may also be decided by the doctor by him or her choosing a stent 520 that provides the desired pressure inside the patient's eye. In one embodiment, the glaucoma stent 520 may be three-dimensionally (3D) printed, and then coated as known in the art.

In one embodiment, the glaucoma stent 520 may be coated with a photosensitizer (e.g., riboflavin) before being implanted into the eye. Then, after the glaucoma stent 520 is implanted in the eye, the photosensitizer (e.g., riboflavin) may be released by the glaucoma stent 520 into the tissue surrounding the stent 520.

Next, turning to FIG. 43, a syringe 536 for implantation of the glaucoma stent 520 will be briefly described. As shown in FIG. 43, the syringe 536 comprises a sharp needle portion 538 for penetrating the tissue, a piston portion 540 for implanting the stent 520 into its desired location, and a plunger 542 for driving the piston 540, which in turn, drives the stent 520 into the tissue of the patient.

Now, referring to the illustrative embodiment of FIGS. 44-46, an exemplary surgical procedure using the stent 520 will be explained. Initially, referring to FIGS. 44-46, it can be seen that the eye 500 undergoing surgery generally includes a cornea 502, an anterior chamber 504, an iris 506, a lens capsule or capsular bag 508 with an intraocular lens 530 disposed therein, lens zonules 510, a vitreous cavity 512, a conjunctiva 514, a sclera 518, a retina 526, and an optic nerve 528.

In FIG. 44, liquid collagen and hyaluronic acid with or without a photosensitizer is initially injected in the subconjunctival space using a needle 544 so as to create a space (i.e., a bleb) for the stent 520. When the solution comprising the liquid collagen and the hyaluronic acid is subsequently cross-linked with ultraviolet light or another wavelength of light, a honeycomb structure is formed in the subconjunctival space around the stent outflow, thereby facilitating the draining of aqueous fluid from the stent. As such, when the stent 520 is subsequently positioned in liquid collagen that is cross-linked at the end of the surgery, the scar forming cells in the Tenon's capsule under the conjunctiva are killed, and the aqueous fluid is capable of diffusing through the stent 520.

Next, the glaucoma stent 520 is implanted into the conjunctiva 514 of the eye 500 using the syringe 536 described above. The syringe 536 is essentially loaded with the stent 520, and then the sharp needle portion 538 of the syringe 536 is used to penetrate the eye wall before the stent 520 is unloaded by the syringe 536. After the stent 520 is delivered into the tissue, the syringe 536 is withdrawn from the eye 500. Once inserted, the glaucoma stent 520 extends from the anterior chamber 504 to the subconjunctival space 515.

The cross-linked subconjunctival space or bleb may be created immediately before the implantation of the stent 520 during a single surgical procedure so as to prepare the space first so that the end of the stent 520 enters the cross-linked subconjunctival space during the surgery. Alternatively, the cross-linked subconjunctival space or bleb may be created during a first surgical procedure, and then the stent 520 may be implanted thereafter during a second, separate surgical procedure. In this alternative embodiment, the second surgical procedure may be performed a significant time after the first surgical procedure. The cross-linked subconjunctival space or bleb may be irradiated using either an external ultraviolet light or a handheld fiber optic connected to a laser that is placed close to the space or bleb and the tissue that will surround the stent 520 (i.e., the corneoscleral tissue). This tissue may be irradiated for 5 to 20 minutes so as to cross-link the tissue.

Then, after the implantation of the stent 520 in the conjunctiva 514 of the eye, the photosensitizer (e.g., riboflavin in a biocompatible fluid) is injected into the eye 500 using a needle 516 (see FIG. 45). That is, similar to that described above, the photosensitizer or cross-linker is injected using the needle 516 into the anterior chamber 504 of the eye 500 after the implantation of the stent 520. The photosensitizer injected from the needle 516 travels through the glaucoma stent 520, and into the subconjunctival space 515 of the eye 500 so that the photosensitizer permeates the tissue surrounding the glaucoma stent 520. After which, at the end of the surgical procedure, the stent 520 and the areas surrounding the stent 520, both inside and outside, are cross-linked. In particular, with reference to FIG. 46, an inflow end of the glaucoma stent 520 proximate to the anterior chamber 504 of the eye 500 is irradiated using a fiber optic 532 carrying ultraviolet (UV) laser light so as to cross-link the tissue surrounding the glaucoma stent 520, thereby preventing fibrosis around the glaucoma stent 520. Also, as shown in FIG. 46, an outflow end of the glaucoma stent 520 in the subconjunctival space 515 of the eye 500 is irradiated using a fiber optic 534 carrying ultraviolet (UV) laser light so as to cross-link the tissue surrounding the glaucoma stent 520, thereby preventing fibrosis around the glaucoma stent 520 outflow.

Next, an illustrative embodiment of a method of implanting a corneal intraocular pressure sensor in an eye of a patient will be described below with reference to FIGS. 47-53. In general, the procedure involves the steps of forming a pocket in a cornea of an eye so as to gain access to tissue surrounding the pocket, applying a photosensitizer inside the pocket so that the photosensitizer permeates at least a portion of the tissue surrounding the pocket, irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and inserting an intracorneal implant comprising a pressure sensor into the pocket after the tissue has been cross-linked. The pressure sensor of the intracorneal implant is configured to measure the intraocular pressure of the eye of the patient. As shown in FIGS. 47-53, the eye 610 undergoing the implantation of the pressure sensor generally includes a cornea 612, an iris 626, a lens 628, and an anterior chamber 632.

Initially, a pocket is formed in the cornea of the eye so as to gain access to tissue surrounding the pocket. In the illustrative embodiment, referring to FIG. 47, a two or three-dimensional portion of stromal tissue is first cut out from the cornea of the eye using a femtosecond laser (i.e., an incision 636 is first cut in the cornea 612 of the eye 610 using the laser beam(s) 634 emitted from the femtosecond laser). Then, the three-dimensional cut portion of the cornea 612 is removed using forceps so as to create a three-dimensional pocket for receiving the intracorneal implant. The formation of the three-dimensional pocket creates a cavity so that, when the intracorneal implant is placed in it, the implant will not exert any pressure on the stromal tissue of the cornea.

In one or more embodiments, an intrastromal corneal pocket is created in the peripheral part of the cornea involving 1 to 4 millimeter (mm) areas in width located between the cornea and the anterior sclera using a femtosecond laser. Prior to the laser application, if needed, the peripheral conjunctival capillaries are bleached out with a low dose of vasoconstrictive medication, such as 0.5% to 1% phenylephrine applied locally with a cotton swab applicator, and/or a low dose (0.1 to 2%) hyaluronic acid in a fluid is applied to make the corneal limbus area transparent.

In one or more embodiments, the three-dimensional pocket 624 formed in the peripheral portion of the cornea extends between 1 degree and 360 degrees around the corneal periphery (refer to the front view of FIG. 51), and the three-dimensional pocket is located at a predetermined distance from the Bowman's membrane in the corneal periphery of the eye.

In one or more embodiments, one or two incisions are used depending on the size of the pocket to access the intrastromal incision. Then, a curved probe is used to separate the remaining corneal adhesion between the walls of the incision, so as to create a pocket for the injection of a photosensitizer (i.e., a cross-linker).

After the three-dimensional pocket 624 is formed, a photosensitizer is applied inside the three-dimensional pocket 624 so that the photosensitizer permeates the tissue surrounding the pocket (refer to FIG. 48). The photosensitizer facilitates the cross-linking of the tissue surrounding the pocket 624. In the illustrative embodiment, a photosensitizer (i.e., a cross-linker), such as riboflavin, is injected with a needle 638 (see FIG. 48) at a concentration of about 0.5% to 4% in a biocompatible fluid, such as a physiological saline solution, etc., in a volume of 0.01 milliliters (ml) to 1 milliliters (ml) as needed for the extent of the pocket 624 to cover the internal walls of the corneal pocket 624 for a desired duration for the photo sensitizer to penetrate at least 20 microns beyond the corneal pocket 624 in the corneal stroma. This will take about a few seconds to about 30 seconds, while avoiding the crosslinking of the entire remaining wall of the cornea 612. In the illustrative embodiment, an effort is made to limit the corneal staining with the photosensitizer to the wall of the pocket 624 so that the photosensitizer never reaches the anterior or posterior full thickness of the cornea 612.

In one or more embodiments, 0.01 milliliters (ml) to 0.1 milliliters (ml) of 0.02 to 2% concentration lidocaine or bupivacaine solution may be injected alone or along with the photosensitizer in the corneal pocket 624 to anesthetize the cornea for a duration of 10 to 15 hours, thereby eliminating pain sensation or discomfort of the surgery.

In one or more embodiments, the width of the corneal pocket 624 may be 1 to 3 millimeters (mm), as needed. The pocket may be circular, semi-circular, C-shaped, doughnut-shaped, rectangular, or any other suitable shape.

Next, in the illustrative embodiment, shortly after the photosensitizer is applied inside the pocket 624, the cornea 612 of the eye 610 is irradiated from the outside using ultraviolet (UV) radiation 640 so as to activate cross-linkers in the portion of the tissue surrounding the three-dimensional pocket 624, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket.

In the illustrative embodiment, ultraviolet (UV) radiation 640 at a desired power of 0.5 to 50 mW/cm2 and a duration 1 to 15 minutes is applied to the cornea 612 of the eye 610 from outside in a stationary manner (see FIG. 49), or using a continuous painting or oscillatory technique with a focused small-sized spots of 1 to 4 millimeters (mm) and high energy to cover the width of the pocket, and to activate the photosensitizer in the corneal pocket 624, and thereby crosslink the collagen of the corneal stroma 642 surrounding the corneal pocket 624, kill all cells located within the cross-linked corneal area while providing a physical stability to the wall of the corneal pocket and preventing the wall from adhering to itself or to a future implant. In other embodiments, if a photosensitizer other than riboflavin is used, radiation with another wavelength of light may be applied to the cornea 612 of the eye 610 to cross-link the collagen of the corneal stroma 642 surrounding the corneal pocket 642.

In one or more embodiments, ultraviolet (UV) radiation at the desired power in a form of stationary or focused light for a duration of 1 to 5 minutes is applied, as needed, depending on the size of the pocket 624, and when using the painting method, the ultraviolet radiation is applied for 1 to 20 minutes depending on the size of the pocket 624. The power used for the UV radiation and the focal spot size of the laser that is used depends on the power of the radiation and the length of the pocket 624. The radiation may be applied externally, or via a fiber optic 644 inserted inside the pocket 624 in a painting fashion (see FIG. 50), so as to activate the photosensitizer and cross-link the collagen of the corneal stroma 642 surrounding the corneal pocket 624, thereby killing all cells located within the cross-linked cornea 642 while preventing encapsulation, cell migration, or rejection of the implant, and also providing an amorphous wall between the implant and the rest of the corneal stroma creating a vascular free zone only to the extent that the cross-linker has penetrated in the cornea surrounding the implant. The radiation is applied a short time after the cross-linker is injected in the pocket 624.

In one or alternative embodiments, the cornea is cross-linked from outside by dropping a cross-linker, such as riboflavin, at concentration of 1-2% in a physiological solution having dextran or hyaluronic acid or chondroitin sulfate over the corneal epithelium or denuded corneal epithelium for a period of time of 15 to 30 minutes. After which, the cornea 612 is cross-linked with the UV laser light for 10 to 50 minutes depending on the power of the UV laser applied, then waiting after cross-linking for a period of 3-4 weeks to implant the intraocular pressure sensor in the cross-linked cornea as described above.

Now, with reference to FIGS. 51-53, it can be seen that, after the portion of the tissue surrounding the pocket 624 has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, an intracorneal implant comprising a pressure sensor 618 is inserted into the three-dimensional pocket 624 formed in the cornea 612 of the eye 610, which is in a location anteriorly disposed relative to the iris 626 and the lens 628. As shown in these figures, in the illustrative embodiment, the intracorneal implant is equipped with a pressure sensor 618, such as a capacitor, located in the corneal periphery of the eye 610. Also, as best shown in the sectional view of FIG. 53, the pressure sensor 618 of the intracorneal implant is equipped with a needle 630 that penetrates the rest of the cornea 612 and opens in the anterior chamber 632 of the eye 610 to measure the intraocular pressure directly by a portion of the sensor 618 being disposed inside the needle 630 without obstructing the central vision through the central cornea 614 (e.g., refer to FIG. 51). Turning to FIGS. 51 and 52, it can be seen that the sensor 618 is equipped with an antenna 622 that can transmit the information about the intraocular pressure for a duration of 24 hours and beyond while a receiver located outside of the eye 610 (e.g, a receiver on a regular eyeglass frame) receives the information and records and/or transmits the information to another remote device. The information is transmitted to a processor that transmits the information on the intraocular pressure uninterruptedly for years after implantation over a substantial distance to a doctor's computer or the patient's computer. The capabilities of the present invention are in stark contrast to the aforedescribed conventional contact lenses that can be carried only for 24 hours on the cornea to measure the intraocular pressure (IOP). If the conventional contact lenses are left on the cornea for a long time (i.e., greater than 24 hours), they can affect the integrity of the cornea, interfere with the oxygen and nutrition of the cornea, and ultimately lead to corneal abrasion or an infection.

In one or more embodiments, two-dimensional or three-dimensional stromal tissue is cut and/or removed with a femtosecond laser depending on the thickness of the sensor 618 and the antenna 622 and the location where the implant will be placed. As such, a pocket space 624 is created for the intracorneal implant to stay in place without exerting pressure on the remaining cornea 612 (see FIG. 52). As described above, after the pocket 624 is formed, it is followed by the cross-linking of the wall of the pocket so that the corneal pocket is cross-linked.

In one or more embodiments, the surface of the intraocular implant is coated with albumin or collagen, or another organic polymer, etc. that can absorb the photosensitizer after the implant is dipped in the photosensitizer and implanted in the corneal pocket. The photosensitizer leaks out of the polymeric coating of the implant into the corneal stroma, and then ultraviolet (UV) radiation at the desired power and duration is applied externally to activate the photosensitizer in the corneal pocket 624 and the implant coating to cross-link the collagen surrounding the implant, while killing all cells located within the cross-linked cornea, providing physical stability to the cornea, preventing the adhesion or gluing of the implant to the surrounding tissue, and preventing fibrous ingrowth or encapsulation, which can lead to an implant rejection. Also, advantageously, the cross-linking of the corneal pocket 624 makes it possible to exchange the implant when needed without the occurrence of much trauma to the cornea 612, because the prior cross-linking eliminates the cells that cause adhesion between the cornea 612 and the implant.

In one or more embodiments, if needed in the postoperative period, the cross-linking of the wall of the intraocular implant can be repeated by injection of riboflavin with a 33 gauge needle in the space between the implant and the wall of the cavity in which the implant resides, and then the cornea 612 with the implant may be subsequently cross-linked with ultraviolet (UV) radiation to prevent encapsulation of the implant that makes the inspection of the implant in the post-operative period difficult.

In one or more embodiments, the intraocular implant has a small diameter needle 630 (see FIG. 53) of 23 to 34 gauge with a capacitor sensor or a nanocomposite pressure sensor disposed in the inside thereof, positioned at a 90 degree angle relative to the body of the implant, and exposed to the aqueous fluid so as to measure the intraocular pressure (IOP) of the eye 610. The pressure sensor 618 of the intraocular implant is operatively connected to the processor of the implant, and to the antenna 622 and radio frequency (RF) generator 620 of the implant (see FIG. 51). The electrical energy for the radio frequency (RF) generator is provided by a small battery that can be charged from outside as it is done with inductive coupling using an electromagnetic field that transfers energy from a transmitter to a receiver, as known in the art. The needle 630 with the capacitor sensor inside it, penetrates the remaining corneal stroma located in the corneal periphery with minimal pressure, and is open to the inside of the anterior chamber 632 (see FIG. 53). In one or more embodiments, the needle 630 is less than 500 microns in length and less than 200 microns in diameter, and remains permanently in the anterior chamber 632 of the eye 610, without exciting a tissue response due to its cross-linked surface and its size, but can also be removed or replaced with ease. The intraocular pressure (IOP) values measured by the capacitor sensor are transmitted to a processor (e.g., a microprocessor), which is operatively coupled with the radio frequency (RF) generator 620, which transmits the information to remote devices by the means of the antenna 622. Because the wall of the corneal pocket 624 is cross-linked, it will not produce a scar around the implant and its sensor 618, radio frequency (RF) generator 620, and antenna 622, thus permitting direct visual inspection of the implant, which is capable of being removed and/or replaced if needed.

In one or more embodiments, the intraocular implant may be assembled during the surgery after the cross-linked pocket 624 is created. Initially, the antenna 622 is placed in the cross-linked pocket 624 that is disposed radially inward from the limbus 616 of the eye 610 (see FIG. 51), and then the sensor 618 and the radio frequency (RF) generator 620 are placed in the corneal pocket 624 and connected to the antenna 622 as a part of a minimally invasive surgery in the corneal periphery. The capacitor sensor is located inside the needle 630, and the tip of the needle 630 is pushed gently in the anterior chamber 632 of the eye 610 so as to measure the intraocular pressure (IOP) directly, continuously, and precisely from the inside of the eye 610. The sensor 618 with small needle 630 and the radio frequency (RF) generator 620 are located in the corneal periphery avoiding interfering with the patient's vision. In contrast to the other aforementioned conventional technologies, this implant does not need an intraocular surgery for its implantation and the natural crystalline lens 628 of the eye 610 does not need to be removed in order to obtain permanent intraocular pressure (IOP) information for the eye 610.

In one or more embodiments, prior to the insertion of the intracorneal implant into the pocket 624 of the eye 610, a predetermined amount of hyaluronic acid or a viscous biocompatible material is injected into the pocket 624 so as to simplify the insertion of the intracorneal implant in the cross-linked pocket 624.

In one or more embodiments, the pressure sensor and transmitter of the intraocular implant are located inside the peripheral cross-linked pocket 624 of the cornea 612 of the eye 610 that does not occupy the central corneal region 614 of the eye 610. Because the central corneal region 614 of the eye 610 remains open with the intracorneal implant, the intraocular pressure (IOP) may also be measured by a Goldmann applanation tonometer placed on the central part 614 of the cornea 612 that is exposed. Because the implant described herein is peripherally disposed, the central corneal region 614 of the eye 610 is not covered by a conventional contact lens pressure sensor, as described above. Therefore, the intraocular pressure (IOP) can be measured by an ophthalmologist in two ways using a Goldman applanation tonometer and by means of the pressure sensor of the intracorneal implant located in the anterior chamber 632 of the eye 610. Advantageously, the ability to take these dual intraocular pressure (IOP) measurements provides a means of comparison between the values obtained by the intraocular pressure sensor and the Goldmann applanation tonometer to correlate or properly adjust the values obtained from the corneal intraocular pressure (IOP) sensor so as to ensure that measurements by the corneal intraocular pressure (IOP) sensor represent the true intraocular pressure (IOP) of the eye 610, and so the corneal intraocular pressure (IOP) sensor is capable of being properly adjusted using the software of the processor of the corneal intraocular pressure (IOP) sensor. The information obtained with the corneal intraocular pressure (IOP) sensor is also capable of being transmitted remotely via the radio frequency (RF) generator 620, and recorded and forwarded to an ophthalmologist who, in turn, can control the intraocular pressure (IOP) by medication or surgery.

In one or more embodiments, the transmitter of the intracorneal implant may be implanted separately from the pressure sensor 618 during the surgery, but then reconnected during the implantation.

Advantageously, the surgical implantation method and the corneal intraocular pressure (IOP) sensor described herein is capable of measuring the intraocular pressure (IOP) all day and night for a long period of time (e.g., weeks, months, or years), and then recording the intraocular pressure data that is measured so that an ophthalmologist can control the intraocular pressure (IOP) of the patient's eye by medication or surgery.

Any of the procedures described herein can be used alone, or in conjunction with, simultaneously with, before or after any other procedure, method or device that would treat or monitor glaucoma, prevent capsular opacification and fibrosis after cataract extraction during cataract surgery and/or prevent fibrosis around a shunt or stent after glaucoma surgery.

Illustrative embodiments of a drug delivery implant and methods using the same will now be described hereinafter. In accordance with the various embodiments described herein, in order to provide the medication to the anterior and posterior part of the eye with a slow release drug system, it is required to create an immune privileged space inside the cornea to keep the cellular response away and prevent production of cytokine by them, and position the device outside the central visual axis so that the device would not interfere with the patient's vision.

In the embodiments described herein, the device is placed in the far corneal periphery so that it will not affect the vision or visual field of the patient, and so that it has created a so-called artificial “immune-privilege” which does not generate an immune response from the body while fluid, soluble medications or nano-particulates and micro-particulates can travel through it. See, for example, FIGS. 63A-70B.

Because of the location of the implant inside the cornea, the released medication bypasses the epithelial barrier of the cornea, while providing medication in a slow manner by diffusion to the anterior part of the cornea, to the sclera, to the conjunctival tissue, and to the posterior segment of the eye including the retina, choroid, and the optic nerve head. This technique can provide similar immune-privileged spaces in other part of the body so that devices implanted there are not encapsulated.

The drug delivery system of the embodiments described herein may be constructed so that it can have direct access to the anterior chamber, if needed, for both obtaining repeatedly a fluid biopsy from the eye or deliver medication(s) directly inside the eye in a fast or slow release manner, or for reducing the intraocular pressure of the eye by creating a minor flow through a porous implanted stent or tube through the corneal limbus without inducing a fibrous encapsulation of the stent. The stent can ameliorate also corneal dryness caused by dry eye syndrome. The stent can also be equipped with a pressure sensor indicating directly the intraocular pressure and communicating it with a radiofrequency device to outside the eye to a receiver or a processor. As one example, as shown in FIG. 62, the implant 744 may comprise a closed end 746 and a needle 748 for tissue penetration so that the implant 744 is capable of being used for taking liquid biopsies. In addition, stem cells or other cells can reside in, for example, a tubular implant, while having access to the oxygen and nutrients through the artificial barrier in an appropriately prepared corneal pocket. However the porous tubular implant permits these cells to migrate elsewhere in the eye or remain in place without being attacked by body's cellular response. Because the cellular body immune response is dependent on the production of the cells close to the implant or a foreign body to be taken up by the dendritic cells of the body at that location by creating a cell free space around the implant made of transparent amorphous cross-linked collagen. The invention of the embodiments described herein has eliminated the incentive for a Major Histocompatibility Complex (MHC) to occur. Because these MHC are present on the cell surface of the body cells to be activated in the production of an immune response. The release of theses cytokines activates the cellular immune system of the body to either eliminate the threat or isolate the device from the body completely by fibrocytes, thereby building a dense membrane (i.e., scar) around the implant. However, the cross-linked collagen permits the diffusion of water and small molecules permitting the needed growth factors from the incorporated stem cells placed inside the tubular implant needed for survival and the health of the cornea, retina etc.

Though this mechanism is very effective and useful, it affects the function of an implant that usually either releases a needed medication or measures or controls the release of a medication (e.g., measuring the blood glucose level and/or releasing insulin according to the glucose level found in the blood, etc.).

In order to isolate an implant in the body while preventing the immune cell to gain access to the device or build a membranous scar tissue around it, a method has been developed to isolate the implant in the body by killing all the cells adjacent to an implant, while maintaining a fluid-filled area around the implant or creating a barrier out of the surrounding tissue containing collagen and cross-linking the tissue in vivo. This barrier protects the implant from the antigen presenting dendritic cells in the tissue, while permitting the soluble medication or nano-sized particulate material to pass through the barrier so as to treat a pathological process in the body. One can also monitor the level of the analytes in the tissue fluid (e.g., aqueous fluid levels of glucose), which is a representative of the blood glucose level in the blood, from which it is originated. Aqueous level of most if not analytes found in the blood and could be used effectively to provide information on the health or disease processes affecting the eye or the body as a whole.

In the embodiments herein, implantation of a drug delivery device is described for the release or monitoring and controlling of a disease process in the eye, while crosslinking the tissue around the implant or implants (if more than one implant is provided). In any of the embodiments described herein, a plurality of drug delivery implants may be used (e.g., for delivering different medications), rather than a single drug delivery implant.

The technology described herein may be applied for any other device implantation in the body regardless of the location in the body. One of the benefits of the technology is that, if the device needs to be replaced, it can be done easily without dealing with the scar tissue formation that otherwise forms and makes the removal or replacement of the implant very complex because the tissue adhesions that usually forms between the tissue and the device.

One can use this concept described herein for diagnosis or therapy in diseases affecting the cornea, a metabolic disorder, genetic disorder, glaucoma, an infection affecting the eye or another portion of the body, a disease or disorder affecting the front or the back part of the eye or the conjunctiva or lens, an aging process, such as dry eye formation, retinal diseases including infective processes, genetic diseases requiring gene therapy (e.g., retinitis pigmentosa, etc. or metabolic disorders such as diabetes, etc.).

In one embodiment, if the media is clear, a two dimensional intrastromal corneal incision is created that is subsequently converted into a pocket in the corneal stroma using a femtosecond laser or a mechanical cutting system. The femtosecond laser passes through the clear media of the cornea. When the laser beam is focused inside the cornea, one can produce a two-dimensional cut or a three-dimensional cut around a thin part of the tissue that is removed to desired space, shape, depth, and location.

In another embodiment, in opaque elastic tissue (e.g., skin), one can use a knife or a syringe needle ending in a sharp cutting tip to cut a pocket in the tissue. If needed, the incision simultaneously involves removal of a three-dimensional tissue surrounding the surgical pocket to create some additional space for the implant using a similar cutting instrument, in the skin or soft tissue. In general, a cut creates a flexible three-dimensional space that can be filled with an implant. The implant is placed inside the needle and can be expelled from the needle by the syringe into the space created by knife.

In one or more embodiments, an injectable anesthetic (e.g., lidocaine or Bupivacaine) in a desired non-toxic preparation or concentration of 0.1-2% or more in a physiologic solution with, but preferably without, a preservatives, is injected in the corneal pocket to anesthetize the cornea postoperatively for a period up to 8-12 hours (e.g., if a PRK procedure is contemplated or after a corneal inlay implantation to prevent pain sensation completely in the postoperative period). This eliminates subjecting the entire corneal epithelium or the conjunctival epithelial cells to the damaging effect of topical anesthesia, which delays corneal re-epithelialization or conjunctival epithelial cells. Generally, the topical preservatives present in the topical anesthesia damages the cells that are bathed in them, and at times affects the regeneration of these cells (i.e., corneal epithelial or conjunctival cells) if applied frequently. Also, it may produce addiction to the topical anesthesia for eliminating the pain sensation caused by the loss of the corneal epithelial cells, whereas the injectable anesthetic does not damage the epithelial cells, including the nerve cells or their axons, except for blocking temporarily the neuronal transmission.

In one or more embodiments, the collagen cross-linker is mixed with the intracorneal locally injectable anesthetic, and injected simultaneously or sequentially in the corneal pocket.

In one or more embodiments, the pocket is filled with a biocompatible implant or implants (if more than one implant is provided) made of organic or non-organic material, or a mixture of it, and the implant is used for drug delivery. The implant may further be coated with a biocompatible material, such as collagen, elastin, polyethylene glycol, biotin and streptavidin, etc., as known in the art, or a composition thereof, to make the implant more biocompatible. The implant and/or the coating can be cross-linked with a cross-linker with the desired thickness and shape before or after implantation.

In one or more embodiments, the diameter of the corneal pocket can be 0.1 to 4 millimeters (mm), as needed. Only flat implants need a larger space with more than 0.2 mm. As shown in FIG. 63A-70B, the pocket can be circular, semicircular, C-shaped, doughnut-shaped, rectangular, or any other shape.

In one or more embodiments, the implant or implants (if more than one implant is provided) can be located at a desired distance from the Bowman's membrane or from the corneal periphery, that is located away from the center of the visual axis (i.e., the implant may be off-centered, or ring-shaped in the peripheral cornea). See, for example, FIGS. 63A-70B.

In one or more embodiments, the implant or implants (if more than one implant is provided). is made to the desired shape, and size in diameter and length that fits with ease inside the corneal pocket without exerting pressure on the corneal tissue (i.e. without bulging it).

In one or more embodiments, a photosensitizer or cross-linker, such as riboflavin, is injected at the desired concentration in a biocompatible fluid or a viscous fluid prior to the implantation of the implant. However, it can be also administered simultaneously with the implant in the corneal pocket sufficiently to cover the internal wall of the pocket for a desired duration so that it penetrates at least 20 micron or wider, taking 5-30 seconds after injection prior to the cross-linking of the cornea, which prevents cell proliferation, encapsulation, or rejection of the implant while preserving an acellular barrier.

In one or more embodiments, ultraviolet (UV) radiation at the desired power (e.g., 1 to 4 mW/mm²) and duration of 1-15 minutes, as needed, depending on the concentration of the photosensitizer or other radiation if another cross-linker is used (e.g., visible or infrared (IR) or another wave length) is applied externally to activate the photosensitizer in the corneal pocket, and to cross-link the collagen of the corneal stroma surrounding the corneal pocket, thereby killing only the cells located within the cross-linked cornea while preventing encapsulation of the drug implant while providing a physical stability to the cornea and preventing the wall of the pocket from adhering together or to the implant. This permits the implant to be replaced, if needed, with another implant with ease.

In one or more embodiments, the implant is coated with an organic material, such as collagen, dipped in a photosensitizer, or the implant can be coated with nanoparticles of the photosensitizer and implanted in the corneal pocket and ultraviolet (UV) radiation is applied with the desired power and duration using a painting technique using a small diameter fiber optic or other radiation with another wave length is applied if another cross-linker is used, externally or internally inside the pocket via a fiber optic to activate the photosensitizer in the corneal pocket and to cross-link the collagen of the corneal stroma surrounding the corneal pocket, thereby killing all cells located within the cross-linked cornea and cross-link the implant simultaneously. The corneal cross-linking prevents implant encapsulation with fibrous tissue, but provides a physical stability to the cornea without gluing the wall of the pocket together or to the implant.

In one or more embodiments, an injection of a small amount of hyaluronic acid in the pocket simplifies insertion of the drug implant in the corneal pocket.

In one or more embodiments, the drug implant has a tube-like structure with a size of 0.01 to 3 micron diameter holes in its wall, or having one micron or larger-sized holes for diffusion of fluid across it.

In one or more embodiments, the implant can be silicone, acrylic, methacrylate, hydroxyethyl methacrylate (HEMA), cross-linked organic or any other biocompatible transparent or non-transparent material, metallic or non-metallic, or a mixture thereof or coating other polymers, such as collagen or elastin with the desired thickness of 2 microns or more, as needed.

In one or more embodiments, the implant is made of various drug delivery polymers, such as polylactic acid or polyglycolic acid, or a combination thereof or polycaprolactone, or chitosan or other organic materials that can deliver the medication at a certain concentrations and dissolve within time ranging from 3-12 months or more.

In one or more embodiments, the biodegradable or non-biodegradable implant can be replaced with another one as before or a non-biodegradable material, but having biocompatible material or coating where the drug release occurs either through the small holes in the body of the implant at a certain rates depending on the size of the holes, or from one or both ends of the implant for drug delivery, as needed.

In one or more embodiments, the implant is a porous biodegradable polymer.

In one or more embodiments, the material inside the tubular implant is liquid, nanoparticles, suspension, powder, porous polymeric drug, etc.

In one or more embodiments, the implant is made using 3-D printing technology to the desired shape, size and/or coated with more biocompatible polymer(s) and cross-linked prior to the implantation, or it is implanted in a cross-linked pocket.

In one or more embodiments, the cross-linked corneal implant can be loaded with one or multiple medications needed for a short biocompatible drug delivery, or prophylactically to prevent an infection, or other used therapeutically medications to treat a disease process (e.g., inflammation, intraocular pressure (IOP), neovascularization, infection, or a cytokine, etc.).

In one or more embodiments, an organic cross-linked material can be used as above for a short term drug delivery of 1 to 4 weeks.

In one or more embodiments, an organic cross-linked material can be used as above for a short term drug delivery of 5 to 50 weeks or longer.

In one or more embodiments, the implant is a C-shaped flexible or semi-flexible structure, and can be implanted in the prepared corneal pocket according to the size or the shape of the implant (e.g., centered around the visual axis having a string shape, rod-like shape, or flat shape), while removing a small 3-D tissue from the stroma for the pocket formation to provide space for the implant for drug delivery to the cornea or the anterior chamber, trabecular meshwork, conjunctiva, or diffusing toward the posterior segment, such as the retina, choroid or the optic nerve of the eye. As shown in FIGS. 54A-54D, the drug delivery implant may be rod-shaped 710, C-shaped 712, two-part semi-circular 714, or one-part semi-circular 716. Also, as illustrated in FIG. 59, the implant may also be in the form of a rectangular flat tube 734. In FIGS. 63A and 63B, a two-part semi-circular drug delivery implant 756 disposed in a cross-linked pocket in the peripheral portion of the cornea 752 that is spaced apart from the central visual axis 754 of the eye so as not to obstruct the central portion of the eye. As shown in FIG. 63B, the two-part semi-circular drug delivery implant 756 is disposed adjacent to the anterior chamber 757 of the eye, and anteriorly with respect to the iris 753 and lens 755 of the eye. In FIGS. 64A and 64B, a generally linear drug delivery implant 760 is disposed in a cross-linked pocket in the peripheral portion of the cornea 752.

Turning to FIGS. 66A and 66B, it can be seen that an eye generally includes a lens 763, an iris 765, cornea 766, an anterior chamber 767, a pupil 768, and a limbus 770. In FIGS. 67A and 67B, a one-part semi-circular drug delivery implant 772 is shown disposed in a cross-linked pocket in the peripheral portion of the cornea 766. In FIGS. 68A and 68B, a doughnut-shaped or ring-shaped drug delivery implant 774 is shown disposed in a cross-linked pocket in the peripheral portion of the cornea 766. In FIGS. 69A and 69B, a generally linear drug delivery implant 776 is shown disposed in a cross-linked pocket in the peripheral portion of the cornea 766.

In one or more embodiments, the implant is inserted in the corneal pocket through a small external incision made into the corneal pocket.

In one or more embodiments, the pocket itself can be filled with biodegradable nanoparticles for drug delivery to the entire ocular structures from the cornea to the optic nerve, and all tissues in between. The medication(s) can be anti-inflammatory, anti-infective, immune-suppressants, AntiVEGFs, biologics, Anti-PDGF, Anti IL-6, Rho kinase inhibitors, nerve growth factors, anti-glaucoma medications, gene(s) delivery in conjugation with viral or non-viral nanoparticles, such as nanoparticles, quantum dots, biodendrimers, etc. coated with polyethylene glycol (PEG) or cell penetrating agents along with an antibody to the specific tissue. This permits the genes or medications to be delivered after their migration out of the implant and the corneal pocket and to attach to the targeted cells in the cornea, conjunctiva, trabecular meshwork, retinal ganglion cells or photoreceptors, retinal and optic glial or nerve cells or their axons etc.

In one or more embodiments, the one or more medications in the drug implant may be anti-inflammatory agents, such as steroids, Dexamethasone, NSAIDS, Anti IL-17, Anti IL-6 and other Anti-ILs or antibiotics, fluoroquinolones, macrolides, cephalosporin A, vancomycin, aminoglycosides, penicillin and its derivatives or combination of antibiotics, etc., anti-virals, ganciclovir, valcyclovir, etc., anti-fungals, amphotericine B, etc., Anti-VEGFs, Avastin, lucentis, Aflilbercept, Anti-IL-6, anti-parasitic, etc., or other anti-inflammatory agents, such as NSAIDs after any corneal surgery and act therapeutically to various diseases affecting the conjunctiva (e.g., dry eye), immune-suppressants, such as cyclosporine A, Mycophenolic acid, anti-proliferative agents, anti-metabolite agents, in uveitis, choroiditis or other medications, such as anti-glaucoma medication or combination of medications, gene delivery, DNA, RNA, siRNA etc. along with viral or non-viral delivery vehicles and CRISPR cas9 mediated homology-independent targeted integration (HITI) or homology directed repair (HDR) to modify the genetic components of various diseases of the eye.

In one or more embodiments, repeated crosslinking of the pocket can be performed as needed to prevent new cellular ingrowth and adhesion around the implant from the corneal tissue so that the implant's barrier is maintained, and the implant can be removed or replaced as needed (e.g., if the eye needs another or a combined medication to regulate disease process, such age related macular degeneration, glaucoma, uveitis, choroiditis or an infectious process of any origin).

In one or more embodiments, the peripheral cross-linked pocket is used to insert or inject medications needed to treat a corneal disease or glaucoma or a disease of the posterior segment. The medication can be in a form of nanoparticles, microspheres, lipid coating or PEG, streptavidin, biotin coating, etc., micelles, liposomes, thermosensitive chitosans, etc.

In one or more embodiments, one can inject or implant in the peripheral corneal pocket large-sized flexible, semi-solid or porous or solid rod, flat or tube or any shape and size polymeric material that can be absorbed with time and the medication is released slowly to the cornea or the anterior chamber of the eye or diffuses to the back of the choroid or retina and optic nerve.

In one or more embodiments, the diameter of these rod or flat-shaped shape implants can vary between 10 microns to 1 millimeter (mm) in diameter or larger with a length of 1 to 50 mm or longer.

In one or more embodiments, the porous tube can be made of semi-permeable non-biodegradable material that permits only the diffusion of the fluid/medication, etc. in and out of the tube, implanted in the peripheral cross-linked pocket. In these one or more embodiments, the tube can be refilled with medication as needed. For example, as shown in FIG. 61, the implant 740 in the form of a rectangular tube is refillable by injection with a needle 742.

In one or more embodiments, the drug implant tube contains stem cells, embryonic stem cells, ciliary hormone producing cells, or other hormone or factors producing stem cells, neuronal or glial stem cells, Mesnchymal stem cells, trabecular meshwork stem cells, limbal stem cells, modified skin stem cells, etc. in a biocompatible fluid that permits nutrition to reach the cells injected in the tube where the cells are immortalized to produce one or the other medication, growth factors, such as ciliary neurotrophic growth factor, RPE growth factor, nerve growth factors, anti-VEGFs, or other medications needed.

In one or more embodiments, the non-biodegradable tube with pores for drug and cell delivery is implanted in a cross-linked pocket with an implant in any part of the body for medication and cell delivery for various medications and functions.

In one or more embodiments, the implant is coated with biocompatible polymer(s) that is used for delivery of stem cells with medication in a corneal pocket. The implant has larger diameter holes of 5 microns and more in its wall permitting the cells to escape from the tubular implant into any tissue (e.g., corneal pocket containing stem cells, embryonic stem cells, ciliary body factor producing stem cells, neuronal or glial stem cells, Mesnchymal stem cells, trabecular meshwork stem cells, Limbal stem cells, modified skin stem cells, etc. in a biocompatible fluid) that permits nutrition to reach the cells injected in the tube where these cells can grow and pass through the holes of the implant and move toward a tissue. In FIG. 57, the tubular implant 726 has small holes 728 disposed in the circular peripheral side thereof, whereas the tubular implant 730 in FIG. 58 has large holes 732 disposed in the circular peripheral side thereof.

In one or more embodiments, the implant contains stem cells, embryonic stem cells, cilliary body hormone producing stem cells, neuronal or glial stem cells, Mesnchymal stem cells, trabecular meshwork stem cells, limbal stem cells, modified skin stem cells, etc. in a biocompatible fluid that permits nutrition to reach the cells injected in the tube along with Rho kinase inhibitors or Nerve growth factors to stimulate their regeneration and migration of theses cell and repair the pathology in the tissue.

In one or more embodiments, genetically modified cells are used to produce needed enzymes and medications. The combination of cross-linking of the cornea and killing the corneal cells and lack of vessels in the corneal makes it a suitable place for these cells in the tube implant to survive inside the tube without being attacked by the cellular body's response, thereby creating an immune privileged space for these cells to survive and produce medications needed locally or systemically (e.g. in many genetic diseases of the cornea such as Fuchs dystrophy, etc.).

In one or more embodiments, the pocket can be filled with a polymeric material that can become more semisolid, or becomes a gel, and contains medication for slow release of medication.

In one or more embodiments, the medication can be injected in the peripheral pocket along with corneal stem cells from the limbus or genetically modified skin stem cells, embryonic or pluripotential stem cells, or mesenchymal stem cells grown in the culture for implantation, in cases of cell loss of endothelium, or in genetically caused corneal opacification, such as macular dystrophy or trauma.

In one or more embodiments, the stem cells are mesenchymal stem cells injected in the corneal pocket along with ROCK inhibitors to replace or repair a cloudiness of the cornea.

In one or more embodiments, the stem cells are nerve cells to induce regeneration of the damaged corneal nerve (e.g., in diabetic patient) and after traumatic corneal injuries or after LASIK surgery.

In one or more embodiments, all tubular drug implants or devices are replaceable with ease.

In one or more embodiments, the tube can be refilled with medication to be used as slow release drug delivery that releases the drug in the cornea and anterior of the posterior segment of the eye.

In one or more embodiments, the tube is used for taking fluid samples from the eye.

In one or more embodiments, one creates an intrastromal corneal pocket in the peripheral cornea involving 2-4 mm 4-8 mm in width areas involving the cornea and the anterior sclera after bleaching out the peripheral conjunctival capillaries with a low dose of vasoconstrictive medication such as 0.5%4% phenylephrine applied locally with a Q-tipped applicator using a femtosecond laser.

In one or more embodiments, a small knife can be used to create a pocket in the cornea or elsewhere under the skin etc. if needed.

In one or more embodiments, the pocket width is more toward the corneal side than the scleral side or vice versa. The circumferential extent of the pocket can be 1 degree to 360 degrees of the corneal periphery (see FIGS. 63A, 63B, 67A, 67B, 68A, and 68B).

In one or more embodiments, using a small incision to access the intrastromal incision, one uses a curved probe to separate the corneal adhesion for injection of a photosensitizer cross-linker, such as riboflavin, at the desired concentration of 0.5%-4% in a biocompatible fluid, such as a physiological saline solution, etc. or suspension of particulates in a volume of 0.01 milliliters (ml) to 1 milliliter (mm) as needed only for the extent of the corneal pocket to cover the internal walls of the pocket for a desired duration that the photosensitizer penetrates at least 20 microns and beyond the corneal pocket in the corneal stroma to isolate that localized area of the cornea from the rest so that it does not respond with cell migration into the surrounding implant and so that it avoids tissue bounding together or to the implant.

In one or more embodiments, 0.01 ml to 0.1 ml of 0.02-2% lidocaine or bupivacaine solution can be injected alone or along with the photosensitizer in the corneal pocket to anesthetize the cornea for the next 1-15 hours, thereby eliminating pain sensation or discomfort of the surgery, and dry eye after surgery.

In one or more embodiments, the width of the corneal pocket can be 1-3 mm as needed. The peripheral corneal pocket can be circular, semi-circular, C-shaped, doughnut-shaped, straight, curved, or any other shape.

In one or more embodiments, the cross-linked pocket can be located at a desired distance from the Bowman's membrane in the corneal periphery.

In one or more embodiments, the ultraviolet (UV) radiation or other appropriate wave length of light at the desired power 0.5-50 mW/Cm2 and duration of 1-15 minutes, or other radiation with another wave length is applied externally in a stationary pattern or as a continuous painting/oscillatory technique with a focused small sized spot of 1-4 mm and a high energy to cover the width of the pocket, or on a painting oscillatory fashion entering the corneal pocket with a small diameter fiber optic and to activate the photosensitizer in the corneal pocket and crosslink the collagen of the corneal stroma surrounding the corneal pocket, and preventing the wall from adhering to itself or to a future implant, while providing a physical stability to the wall of the corneal pocket and preventing cell migration and rejection of an implant.

In one or more embodiments, ultraviolet (UV) radiation at the desired power in a stationary or focused light for a duration of 10 seconds to 15 minutes for the stationary radiation, or for a duration of 10 seconds to 20 minutes for the painting approach, depending on the power of the radiation and the length of the pocket used (or other radiation with another photosensitizer and wave length) is applied externally or via a fiber optic inserted inside the pocket to activate the photosensitizer and cross-link the collagen of the corneal stroma surrounding the corneal pocket while preventing cell migration, encapsulation, or rejection of the implant and protecting the anterior corneal stroma and the stem cells.

In one or more embodiments, the corneal pocket is three-dimensionally cut in order to remove a part of the stroma and create a space for the implant.

In one or more embodiments, the wall of the corneal pocket can absorb the photosensitizer from the implant after it is dipped in a photosensitizer solution or the implant is coated with nanoparticles of the cross-linker and placed in the corneal pocket to leak out, which is then followed by UV radiation at the desired power and duration or other radiation with another wave length applied externally or internally via a fiber optic to activate the photosensitizer in the corneal pocket and cross-link the collagen surrounding the implant. This technique provides a physical stability to the cornea preventing adhesion or gluing the implant to the surrounding tissue and preventing fibrous ingrowth or encapsulation or rejection of the implant, which can lead to implant rejection. This makes it possible to exchange the implant when needed without much trauma to the cornea surrounding the implant.

In one or more embodiments, the photosensitizer is conjugated to the surface of the implant having a polymeric coating, such as collagen, that releases the photosensitizer (e.g., riboflavin) from the implant once it is exposed to the water content of the tissue in the corneal pocket surrounding it. The riboflavin is released and stains the wall of the implant which is subsequently cross-linked with UV light. This prevents tissue adhesion between the implant and the corneal tissue and maintains a potential space between the corneal wall and the implant, thereby preventing activation of an immunologic response or neovascular tissue response by releasing from the tissue vascular endothelial cell factors (VEGF) in response to a foreign implant. The cross-linking process can be repeated as needed every 6 months to a year or more as needed. The cross-linking of the collagen protects the implant containing particulate medication(s), which releases the drug for a long time, and prevents the pocket from being invaded by the immune cellular elements and keeps the lumen of the tube shaped implant open.

In one or more embodiments, during the cross-linking, the corneal pocket remains pristine not allowing cell traffic or access to the pocket surrounded by the cross-linked amorphous collagen or other cross-linked tissues located in that area.

In one or more embodiments, the crosslinking can be repeated again in the postoperative period after implantation by injecting a cross-linker in the corneal pocket through a needle inside the wall of the pocket, which diffuses readily through the potential space around the implant and the wall of the pocket, and then is irradiated with UV light from the outside.

In one or more embodiments, the implant can be made of silicone, acrylic, methacrylate, HEMA, metallic or non-metallic, synthetic, organic, polymeric biodegradable, etc., coated with another or a biocompatible polymeric materials or a mixture thereof or coated with, for example, collagen or elastin, formed with a desired thickness of 2 microns to 100 microns, and conjugated with a cross-linker or the cross-linker is injected in the potential pocket space in the tissue and is cross-linked.

In one or more embodiments, the implant is made by the use of 3-D printing technology with the desired material, shape, size or thickness, transparent or non-transparent organic or non-organic or a mixture of them, a material such as collagen elastin, synthetic polymers can be coated again with riboflavin nanoparticles with one or more biocompatible polymer(s), and cross-linked with UV light prior to or preferably after implantation.

In one or more embodiments, the implant is coated with a collagen polymer to a desired thickness or in combination with another polymer, such as polyvinyl alcohol, chitosan, polycaprolactone, etc., conjugated with riboflavin or another cross-linker and cross-linked before or after implantation in a preformed pocket with an appropriate wavelength of light or UV radiation to cross-link the polymeric coating inside the body allowing the cross-linker to be released in the tissue, and then cross-link the tissue surrounding the implant in order to, after implantation, release the incorporated medication from the implant slowly without inciting cellular attraction or encapsulation of the implant which inhibits a release of the medication(s) from the implant that is unpredictable. For example, as shown in FIG. 55, the implant 718 is coated with a polymer and/or a photosensitizer.

In one or more embodiments, the non-biodegradable flexible porous tube made of polymeric material or a non-organic compound in combination with cross-linked organic polymer coating is filled with microspheres, drug nanoparticles incorporated in a polymeric material, such as polylactic glycolic acid, chitosan, liposomes, polycaprolactone, or lipid-coated nanoparticles, etc. containing the medication so as to release the medication slowly from the tube implant.

In one or more embodiments, the implant can serve as a reservoir that releases the medications though the pores of 1 to 3 microns in diameter in its wall, and then can be refilled repeatedly by injecting in the tubular implant the medication through a 33-34 gauge needle through the cornea surrounding the tube.

In one or more embodiments, the implant releases immunosuppressive agents, such as cyclosporine, calcineurin inhibitors, mycophenolic acid, tacrolimus, siraliums, steroids, MPP inhibitors, NSAIDs, antimetabolytes, polycolonal antibodies, monocolonal antibodies, TNF inhibitors, Fingolimod, antibiotics, intraocular pressure (IOP) lowering agents, such as Rho kinase inhibitors, Fasudil, and other agents, pilocarpine, prostaglandin analogues, Brimonidine, etc., anti-virals, Anti-VEGFs, biologics, or neuroprotective releasing medication. The medications being released as needed at concentrations of nanograms or micrograms or mg/per hour depending on the polymeric material size of the holes, length of the polymer, etc.

In one or more embodiments, the implant can be positioned at any place in the body to control a function or release a medication without being encapsulated by the surrounding tissue, due to the cross-linking of the polymeric coating or the pocket being cross-linked prior to the implantation, while the medication can be an anti-VEGF, neuroprotective agents, such as nerve growth factors, Rho kinase inhibitor such as Fasudil, antibiotics, antiproliferative agents, anti-inflammatory agents, etc. at a non-toxic, beneficial concentration.

In one or more embodiments, the implant is made using 3-D printing technology to the desired shape, size or thickness from any material coated with collagen, elastin, or made of collagen, elastin, etc. or synthetic polymers which are further coated with more biocompatible polymer(s), such as acrylic, organic, etc., which are cross-linked prior to the implantation or coated with a cross-linker or the crosslinking nanoparticles are done subsequent to its release in the tissue prior to radiation with the UV light. In another embodiment, the implant is formed from glass using 3-D printing technology (i.e., the implant is 3-D printed glass).

In one or more embodiments, the implant is implanted in another part of the eye, such as under the conjunctiva, under the sclera, in the retina or sub-retinal space, under the skin using an implant containing medications such as Botox, or in other parts of the body using an implant which is coated with collagen to a desired thickness, dipped in a photosensitizer or has photosensitizer nanoparticles, such as riboflavin, etc. or the photosensitizer is injected surrounding the implant and implanted in desired location, such as under or over the sclera in the choroid, under the conjunctiva, etc. Then, ultraviolet (UV) radiation or another wavelength of light is used to cross-link the tissue at the desired power and duration depending on what technique is used. In these conditions, a focused UV or another wavelength of light is applied externally, in a painting oscillatory fashion only to the desired areas or internally through a fiber optic, etc. to activate the photosensitizer in the surrounding tissue where the implant is located. The cross-linked collagenous tissues surrounding the implant prevent creating an adhesion between the tissue and the implant or gluing the wall of the pocket together or to the implant. The cross-linked collagenous tissues surrounding the implant also have these additional benefits: (1) it is easier to replace the implant if needed, (2) fibrous ingrowth or encapsulation is prevented, (3) it permits injection of the cross-linker again to repeat the cross-linking process if needed, and (4) it prevents rejection of the implant and contributes to the slow release of the medication from the implant. Also, these implants can act as a shunt for glaucoma, or drainage shunt for cerebrospinal fluid, or other part of the body, such as a bladder neck for urine if the drainage system is provided with a unilateral valve that only opens when the bladder pressure increases to certain level, etc.

In one or more embodiments, the injection of a small amount of hyaluronic acid or other viscous fluid in the pocket simplifies the inserting of the implant in the peripheral corneal pocket or a pocket created in another tissue.

In one or more embodiments, the implant can be a biodegradable polymer carrying various medications and can be replaced.

In one or more embodiments, the implant is a tube-like structure having a thickness or diameter of 0.02 millimeters (mm) to 0.4 millimeters (mm) in one direction and up to 8 mm in another (flat) width, and being 1-60 mm long covering the entire corneal periphery without pressing the corneal tissue in any direction. The implant may be filled with a medication(s), a fluid, or a combination of them.

In one or more embodiments, the tube is not biodegradable having holes made in the wall of the tube with 0.2 to 3 microns in diameter, or 5 microns to 500 microns in diameter, to permit diffusion of the medications or cells placed in it to produce desired needed proteins, hormones, nerve growth factors, or other products needed for other body cell survival, such as cornea, retina, brain, etc.

In one or more embodiments, the tube has holes that are 5 to 15 microns in diameter so as to permit stem cells to exit the tube. The tube can be biodegradable implanted in a lightly cross-linked corneal pocket permitting, for example, stem cells to proliferate and/or migrate to the cornea. The stem cells can be obtained from limbal stem cells or mesenchymal stem or skin and cultured cells prior to the injection in the cornea or in another part of the body.

In one or more embodiments, the device is implanted in the wall of the vitreous cavity with one end closed and one end open to the vitreous cavity, or the implant can be under the retina or it can penetrate both the retina and the choroid and permit release of medication or the cells.

In one or more embodiments, the implant is implanted in the tissue surrounding the eye, on the face, etc. with one end closed and one end open to the tissue. The implant can be removed after the drug is released, and then replaced.

In one or more embodiments, the repeated crosslinking of the tissue surrounding the pocket can be performed as needed to prevent cellular ingrowth, and the implant can be removed and replaced as needed (e.g. in age related macular degeneration) to maintain delivery of the anti-glaucoma medication, anti-VEGFs, immunosuppressive or anti-inflammatory agents, or nerve growth factors, or Rho kinase inhibitors.

In one or more embodiments, the peripheral cross-linked pocket is used to insert or inject medications needed to treat a corneal disease, glaucoma, or a disease of the posterior segment. The medication can be in a form of nanoparticles, microparticles, micelles, liposomes, chitosans, polycaprolactone as nanoparticles, dendrimers, etc.

In one or more embodiments, one can inject or insert an implant in the peripheral corneal pocket that is in the form of a large-sized flexible, semi-solid or solid, porous or solid rod-shaped implant, a flat implant, or tube-shaped implant that contains medication, or any shape and size polymeric material that can be absorbed with time and the medication is released slowly to the cornea or the anterior chamber of the eye or diffuses through the anterior chamber or through the sclera to the back of the eye, for treatment of the choroidal or retina and optic nerve diseases. As shown in FIGS. 56A-56C, the implant may be in the form of a solid implant 720, a porous implant 722, or a solid tubular implant 724 with an open end. Also, as shown in FIG. 60, the implant may be in the form of a semi-solid or silicone tubular implant 736 with one closed end 738 and one open end 739.

In one or more embodiments, the diameter of the rod or flat-shaped implant can have a length of 1 microns to a few millimeters (mm), or the length can be 1 to 40 millimeters (mm) or longer.

In one or more embodiments, the non-biodegradable tube is open-ended so that the medication exits only from one or both ends of the tube.

In one or more embodiments, the medication can be released for a duration of from 3 months to 3 or more years, such as when containing nanoparticles of fluoroquinolone dexamethasone, diclofenac, etc., and the implant can be replaced or removed if the desired effect has been achieved or reinjected in the corneal pocket.

In one or more embodiments, the tube is closed ended, but has pores for diffusion of the medication. For example, refer to the implants 726, 730 in FIGS. 57 and 58.

In one or more embodiments, the implant can be placed near any joint in the body and the cross-linking is done using ultraviolet (UV) radiation through the skin or through the fiber optic as described for localized drug delivery.

In one or more embodiments, the porous tube can be made of semipermeable non-biodegradable material that permits only the diffusion of fluid/medication, etc. in and out of the tube, and the tube is implanted in the peripheral cross-linked corneal pocket, wherein the tube can be refilled with medication as needed via an injection using a 33-34 gauge needle. For example, refer to FIG. 61.

In one or more embodiments, the tube contains cells in a biocompatible fluid that permits nutrition to reach the cells which are injected in the tube where the cells are immortalized to produce one or more medications, growth factors, such as a ciliary neurotrophic growth factor, RPE growth factor, nerve growth factors, anti-VEGFs, or other medications needed.

In one or more embodiments, the implant contains genetically modified cells producing other needed enzymes and medications. The combination of crosslinking of the cornea produces a wall of amorphous, acellular collagen and the corneal location that lacks vessels provides a suitable place for these cells in the tube implant to survive and produce medications as needed, which otherwise would have to be given repeatedly either locally or systemically, and in many genetic diseases of the cornea, such as Fuchs dystrophy, the cells have to be injected in the subconjunctival space where the cells could be attacked by the normal cellular body's immune response. The cross-linked pocket with the implant creates an immune-privileged space in the cornea or elsewhere for these cells to survive. For example, refer to FIGS. 63A-70B.

In one or more embodiments, the medication in the implant can be in any form or composition, such as antibiotics, anti-inflammatory, immune suppressants, anti-glaucoma medication, anti-vascular proliferation, stimulatory, such as Rho inhibitors. The polymers can be made of bio-degradable compounds, such as polylactic, polyglycolic acid or a combination of them, polycaprolactone, etc.

In one or more embodiments, the corneal cross-linked pocket contains a tubular implant filled with particulate immunosuppressive agents, such as cyclosporine etc., that release the medication at a constant, but low concentration of micrograms as needed. The medication diffuses in the cornea, sclera, and/or conjunctiva, thus eliminating the burning sensation of topical cyclosporine drops and the need for daily drop admiration in dry eye syndromes, or after refractive surgery or other diseases.

In one or more embodiments, the medication can be injected in the peripheral pocket along with corneal stem cells taken from the limbus or genetically modified stem cells and grown in the culture for implantation.

In one or more embodiments, as shown in FIGS. 65A and 65B, a non-biodegradable implant tube 762 as described herein is implanted in the cross-linked corneal pocket of the cornea 752 of the eye with iris 753 and lens 755, and the implant tube 762 is connected to the anterior chamber 757 with the aqueous fluid via a thin 23-34 gauge needle 764, where biomarkers such as VEGFs, glucose, and analytes, etc. are present both inside the aqueous and the tube system made of soft silicone. Similarly, as depicted in FIGS. 70A and 70B, an implant 778 is implanted in the cross-linked corneal pocket of the cornea 766 of the eye with iris 765, and the implant 778 is connected to the anterior chamber 767 with the aqueous fluid via a needle 780. The implants 762, 778 can be penetrated with a 30-34 gauge needle from outside and the aqueous can be aspirated in a volume of less than 0.50 microliters repeatedly over a long period of time without causing a collapse of the anterior chamber. The volume of the anterior chamber is 25 times more than the sample fluid taken. The minimal amount of aqueous fluid withdrawn will be replaced by the eye in less than 10 minutes. This provides a means of obtaining easily a fluid biopsy repeatedly from the eye without penetrating the entire cornea or the eye wall directly with the complication of iris or lens injury and retinal injury. The fluid sample can be examined in chronic disease processes, such as uveitis for biomarker of a disease, viral infection that persist in the eye long after the body has healed, such as Ebola, Zika, Herpes viruses or other viral diseases or non-viral infections that can be detected and treated appropriately. The biomarkers can be obtained from the implanted tube, and can provide valuable information on many metabolic diseases of the body or the eye, a systemic disease (e.g., Alzheimer disease), age related macular degeneration, glucose level, or other analytes (e.g. diabetes) in diabetic retinopathy and other slow progressive degenerative eye diseases, tumors, infection, uveitis, poisoning or drug overdose, etc.

In one or more embodiments, a plurality of implants are implanted in the cornea of the eye. In these one or more embodiments, each of the implants is used for a different purpose. For example, a first one of the implants may be in form of a corneal drug delivery implant used for delivering one or more medications to the eye, as described above. A second one of the implants may be used for taking liquid biopsies from a portion of the eye, as described herein (e.g., extracting a liquid biopsy of the aqueous fluid from the anterior chamber of the eye). A third one of the implants may be used for stem cell delivery and/or gene therapy in the manner described above. A fourth one of the implants may be used for measuring the intraocular pressure of the eye of the patient (e.g., intracorneal implant comprising a pressure sensor 618 illustrated in FIGS. 52 and 53). That is, the fourth implant may contain a pressure sensor configured to measure an intraocular pressure of an eye and to output a signal based on the measured intraocular pressure of the eye, the pressure sensor configured to be implanted in a cornea of the eye; a processor operatively coupled to the pressure sensor, the processor configured to generate intraocular pressure data based upon the signal outputted by the pressure sensor; and a transmitter device operatively coupled to the processor, the transmitter device configured to transmit the intraocular pressure data generated by the processor to a remote receiver located outside of the eye, the transmitter device configured to be implanted in the cornea of the eye. In addition to the pressure sensor, the third implant may further comprise a needle configured to penetrate a posterior portion of the cornea of the eye, the needle configured to open into the anterior chamber of the eye so as to measure the intraocular pressure of the eye without obstructing vision through the central cornea.

In one or more embodiments, one can measure the amount of VEGF present in the aqueous providing information on the disease progression requiring treatment (e.g., anti-VEGFs or no treatment). Anti-VEGFs or another medication can be administered directly in the tube to reach the posterior segment avoiding repeated intraocular injection through the sclera, without having the risk of retinal detachment or lens injury. As another example, liquid biopsy of aqueous in a patient with diabetic retinopathy, where the retina is in need of treatment with the laser coagulation, provides the information regarding whether the disease process is under the control or not.

In one or more embodiments, for the first time one can obtain from the aqueous biopsy, instant information needed for the doctor to diagnose a disease process at the bedside and be able to follow the process over a long period of time with ease.

In one or more embodiments, nanoparticles carrying other medications can be delivered as slow release nanoparticles from the tube in the anterior chamber to treat glaucoma for a long period of time, thereby eliminating the need for repeat therapy. These medications may include pilocarpine, prostaglandin analogues for treatment of glaucoma, Rho kinase inhibitors, or neuroprotective agents or Brimonidine, etc.

In one or more embodiments, the implanted tube is filled with desired medications, as described above, and is coated with collagen or albumin loaded with riboflavin particles that are diffused after implantation in the pocket. The ultraviolet (UV) radiation used for cross-linking permits the diffusing of the medication from the implant as a slow release device, and prevents vascular growth around the implant containing the medication.

In one or more embodiments, the implanted tube can be 100 microns to 1 millimeters (mm) in diameter and 4 mm to 40 mm long, or less than 100 micron in diameter and no longer than a few millimeters in length. The implanted tube maybe filled with any desired medication to be implanted in any tissue and cross-linked after implantation.

Any of the features, attributes, or steps of the above described embodiments and variations can be used in combination with any of the other features, attributes, and steps of the above described embodiments and variations as desired.

Although the invention has been shown and described with respect to a certain embodiment or embodiments, it is apparent that this invention can be embodied in many different forms and that many other modifications and variations are possible without departing from the spirit and scope of this invention.

Moreover, while exemplary embodiments have been described herein, one of ordinary skill in the art will readily appreciate that the exemplary embodiments set forth above are merely illustrative in nature and should not be construed as to limit the claims in any manner. Rather, the scope of the invention is defined only by the appended claims and their equivalents, and not, by the preceding description. 

The invention claimed is:
 1. A method of implanting a corneal drug delivery implant in an eye of a patient, said method comprising: coating an outer surface of a corneal drug delivery implant with an organic material configured to absorb a photosensitizer; forming a pocket in the cornea of the eye so as to gain access to tissue surrounding the pocket; after the pocket in the cornea has been formed, applying a photosensitizer to the pocket so that the photosensitizer permeates at least a portion of the tissue surrounding the pocket, the photosensitizer facilitating cross-linking of the tissue surrounding the pocket; inserting the corneal drug is delivery implant into the pocket, the corneal drug delivery implant configured to slowly release one or more medications into the eye of the patient without being inhibited by vascular growth around the corneal drug delivery implant; and after the corneal drug delivery implant is inserted into the pocket, irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket.
 2. The method according to claim 1, wherein the step of forming a pocket in the cornea of the eye further comprises: cutting out a three-dimensional portion of stromal tissue from the cornea of the eye using a femtosecond laser; and removing the three-dimensional cut portion of the cornea using forceps so as to create a three-dimensional pocket for receiving the corneal drug delivery implant so that the corneal drug delivery implant does not exert any pressure on the stromal tissue of the cornea.
 3. The method according to claim 2, wherein the three-dimensional pocket is formed in a peripheral portion of the cornea between the cornea and the anterior sclera of the eye.
 4. The method according to claim 3, wherein the three-dimensional pocket formed in the peripheral portion of the cornea extends between 1 degree and 360 degrees around the corneal periphery.
 5. The method according to claim 2, wherein the three-dimensional pocket has a width between approximately 0.05 millimeters and approximately 8 millimeters, inclusive.
 6. The method according to claim 1, wherein the step of applying the photosensitizer to the pocket comprises injecting the photosensitizer inside the pocket using a needle such that the photosensitizer penetrates at least 20 microns beyond a wall of the pocket in the stromal tissue of the cornea, the photosensitizer comprising riboflavin.
 7. The method according to claim 6, further comprising the step of: injecting 0.01 milliliters to 0.1 milliliters of a 0.02 to 2% lidocaine or bupivacaine solution alone or together with the photosensitizer so as to anesthetize the cornea for between 1 to 15 hours, thereby eliminating a pain sensation or discomfort during the surgical procedure.
 8. The method according to claim 1, wherein the step of creating a pocket in the cornea of the eye further comprises forming a circular-shaped pocket, a semi-circular-shaped pocket, a C-shaped pocket, a doughnut-shaped pocket, or a rectangular-shaped pocket in the cornea of the eye, and removing the tissue inside the circular-shaped pocket, the semi-circular-shaped pocket, the C-shaped pocket, the doughnut-shaped pocket, or the rectangular-shaped pocket.
 9. The method according to claim 1, wherein the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises irradiating the cornea with ultraviolet light, another wavelength of light, microwaves, or combinations thereof.
 10. The method according to claim 1, wherein the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises inserting a fiber optic into the pocket and irradiating the cornea with light emitted from the fiber optic so as to activate the cross-linkers in the portion of the tissue surrounding the pocket.
 11. The method according to claim 1, wherein the step of irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket comprises irradiating the cornea from outside the eye.
 12. The method according to claim 1, wherein the corneal drug delivery implant is formed from a biocompatible organic material, a biocompatible non-organic material, or a combination of a biocompatible organic material and a biocompatible non-organic material, and wherein the corneal drug delivery implant has a solid structure, a tubular structure, or a porous structure.
 13. The method according to claim 1, wherein the corneal drug delivery implant is formed from polylactic acid, polyglycolic acid, polycaprolactone, another biodegradable polymer, silicone, acrylic, methacrylate, hydroxyethyl methacrylate (HEMA), a metallic material, a non-metallic material, or combinations thereof.
 14. The method according to claim 1, wherein the corneal drug delivery implant is coated with a biocompatible material, the biocompatible material selected from the group consisting of collagen, elastin, polyethylene glycol, biotin, streptavidin, and combinations thereof.
 15. The method according to claim 1, further comprising the step of: replacing the corneal drug delivery implant in the pocket with a replacement corneal drug delivery implant after the corneal drug delivery implant is no longer functional or when the medication in the corneal drug delivery implant has been exhausted.
 16. A method of implanting a corneal drug delivery implant in an eye of a patient, said method comprising: forming a pocket in the cornea of the eye so as to gain access to tissue surrounding the pocket; after the pocket in the cornea has been formed, applying a photosensitizer to the pocket so that the photosensitizer permeates at least a portion of the tissue surrounding the pocket, the photosensitizer facilitating cross-linking of the tissue surrounding the pocket; irradiating the cornea so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket; and before or after the portion of the tissue surrounding the pocket has been stiffened and is devoid of cellular elements by the activation of the cross-linkers, inserting a corneal drug delivery implant into the pocket, the corneal drug delivery implant configured to release one or more medications into the eye of the patient, the corneal drug delivery implant further comprising a needle configured to fluidly couple the corneal drug delivery implant with the aqueous fluid in the anterior chamber of the eye; and wherein the method further comprises the step of: penetrating the anterior chamber of the eye using the needle, an open end of the needle opening into the anterior chamber of the eye so as to allow the medication from the corneal drug delivery implant to be delivered to the anterior chamber of the eye and/or enable an aqueous biopsy to be obtained from the aqueous fluid of the eye.
 17. The method according to claim 1, further comprising the step of: after the implantation of the corneal drug delivery implant, applying the photosensitizer one or more additional times inside the space between the corneal drug delivery implant and the surrounding corneal tissue, and irradiating the cornea one or more additional times with ultraviolet radiation to cross-link the tissue surrounding the corneal drug delivery implant so as to prevent encapsulation of the corneal drug delivery implant and cellular migration towards the corneal drug delivery implant.
 18. The method according to claim 17, wherein the step of applying the photosensitizer one or more additional times inside the space between the corneal drug delivery implant and the surrounding corneal tissue further comprises injecting the photosensitizer inside the space between the corneal drug delivery implant and the surrounding corneal tissue by using a 33 gauge needle.
 19. The method according to claim 1, wherein the corneal drug delivery implant comprises a tubular body portion with a circular sidewall and oppositely disposed ends, the circular sidewall of the tubular body portion being solid and one of the oppositely disposed ends being open or the circular sidewall of the tubular body portion comprising a plurality of holes therein and the oppositely disposed ends being solid.
 20. The method according to claim 1, further comprising the step of: prior to the implantation of the corneal drug delivery implant, constructing the corneal drug delivery implant in vitro by three-dimensionally printing the corneal drug delivery implant to a desired shape and size.
 21. The method according to claim 1, further comprising the step of: prior to the implantation of the corneal drug delivery implant, forming the corneal drug delivery implant into a shape selected from the group consisting of a rod shape, a C-shape, a semi-circular shape, a doughnut shape, and a rectangular flat tube shape.
 22. The method according to claim 1, wherein the medication of the corneal drug delivery implant is selected from the group consisting of an anti-inflammatory, an anti-infective, an immune-suppressant, an anti-VEGF, a biologic, an anti-PDGF, an Anti IL-6, a Rho kinase inhibitor, brimonidine, a nerve growth factor, an anti-glaucoma medication, and combinations thereof.
 23. The method according to claim 1, wherein the corneal drug delivery implant is used for gene delivery with viral or non-viral antibody coated nanoparticles conjugated with DNA, RNA, or siRNA, and CRISPR/cas9 mediated homology-independent targeted integration (HITI) or homology directed repair (HDR) is used to modify the genetic components of various structures of the eye.
 24. The method according to claim 1, wherein the medication of the corneal drug delivery implant comprises one or more medications selected from the group consisting of anti-inflammatory agents, Dexamethasone, NSAIDS, Anti IL-17, Anti IL-6, other Anti-ILs, antibiotics, fluoroquinolones, macrolides, cephalosporin A, vancomycin, aminoglycosides, penicillin and its derivatives, anti-virals, ganciclovir, valcyclovir, anti-fungals, amphotericine B, anti-VEGFs, Avastin, lucentis, Aflilbercept, anti-parasitics, immune-suppressants, Mycophenolic acid, cyclosporine, a Rho kinase inhibitor, a Wnt inhibitor, anti-proliferative agents, anti-metabolite agents, anti-glaucoma medications, and combinations thereof.
 25. The method according to claim 1, wherein the corneal drug delivery implant comprises a plurality of stem cells, the plurality of stem cells selected from the group consisting of embryonic stem cells, ciliary hormone producing cells, neuronal stem cells, glial stem cells, Mesenchymal stem cells, trabecular meshwork stem cells, limbal stem cells, skin stem cells, and combinations thereof; and wherein the plurality of stem cells are provided in a biocompatible fluid that permits nutrition to reach the plurality of stem cells in the corneal drug delivery implant where the stem cells are immortalized to produce one or more medications or growth factors.
 26. The method according to claim 25, wherein the corneal drug delivery implant comprises a tubular body portion with a circular sidewall and oppositely disposed ends, the circular sidewall of the tubular body portion comprising a plurality of holes that are sufficiently sized so as to permit the stem cells to escape from corneal drug delivery implant and to enter the tissue surrounding the tubular body portion of the corneal drug delivery implant and tissue beyond the tubular body portion of the corneal drug delivery implant.
 27. The method according to claim 1, wherein the medication of the corneal drug delivery implant comprises one or more medications selected from the group consisting of immunosuppressive agents, calcineurin inhibitors, mycophenolic acid, tacrolimus, siraliums, steroids, NSAIDs, antimetabolytes, polycolonal antibodies, monocolonal antibodies, TNF inhibitors, Rho inhibitors, Wnt inhibitors, fingolimod, brimonidine, antibiotics, intraocular pressure (IOP) lowering agents, pilocarpine, prostaglandin analogues, anti-virals, anti-VEGFs, biologics, neuroprotective medications, and combinations thereof.
 28. The method according to claim 1, further comprising the step of: refilling the corneal drug delivery implant in the pocket with the medication by using a needle to inject the medication into the corneal drug delivery implant.
 29. The method according to claim 1, wherein the corneal drug delivery implant is formed from polymeric nanoparticles, micelles, liposomes, dendrimers, or combinations thereof.
 30. The method according to claim 1, wherein, in addition to implanting the corneal drug delivery implant with the one or more medications into the pocket, the method further comprises implanting one or more additional implants in the cornea, the one or more additional implants selected from the group consisting of: (i) a biopsy implant for taking liquid biopsies from a portion of the eye, (ii) a stem cell implant for delivering therapeutic stem cells to the eye of the patient, (iii) a gene therapy implant for delivering therapeutic genes to the eye of the patient for treating degenerative or genetic diseases, (iv) a pressure sensor implant for measuring the intraocular pressure of the eye of the patient, and (v) any combination including one or all of the additional implants.
 31. A method of implanting a drug delivery implant in a body portion of a patient, said method comprising: forming a pocket in the body portion of the patient so as to gain access to tissue surrounding the pocket; coating an outer surface of a drug delivery implant with an organic material configured to absorb a photosensitizer; immersing the drug delivery implant in a biocompatible solution comprising the photosensitizer so that the photosensitizer is able to diffuse out of the organic material coating of the drug delivery implant after the drug delivery implant is inserted into the pocket, the biocompatible solution comprising riboflavin nanoparticles; inserting the drug delivery implant into the pocket, the drug delivery implant configured to slowly release one or more medications into the body portion of the patient without being inhibited by vascular growth around the drug delivery implant; and after the drug delivery implant is inserted into the pocket, irradiating the body portion of the patient so as to activate cross-linkers in the portion of the tissue surrounding the pocket, and thereby stiffen a wall of the pocket and kill cells in the portion of the tissue surrounding the pocket.
 32. The method according to claim 31, wherein the step of inserting the drug delivery implant into the pocket comprises implanting the drug delivery implant in one or more eye locations selected from the group consisting of under the conjunctiva, under the sclera, over the sclera in the choroid, in the retina, and in the sub-retinal space.
 33. The method according to claim 31, wherein the step of inserting the drug delivery implant into the pocket comprises implanting the drug delivery implant in a wall of a vitreous cavity of an eye of the patient with one end of the drug delivery implant being open to the vitreous cavity so as to permit the release of medication into the vitreous cavity.
 34. The method according to claim 31, wherein the method further comprises the step of: cross-linking the drug delivery implant before or after the step of implanting the drug delivery implant into the body portion of the patient. 